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BACKGROUND OF THE INVENTION
1. Field of the Invention
The present invention relates to a medical instrument for examining newborn
babies and more particularly to a calibrated optical-electro instrument
for objectively determining the degree of jaundice in newborn babies.
2. Description of the Prior Art
The medical profession is aware of the importance of determining the
existence of jaundice immediately after the birth of a baby. A large
number of newborn children exhibit some degree of jaundice and frequently
a jaundice test is performed as a regular routine in the delivery room.
The degree of jaundice can range from a physiologically permissible level
which will disappear within a short period of time after the birth to
various severe degrees of jaundice, progressing to nuclear jaundice which
can result in the death of a newborn or cerebral palsy as sequela even
when the child is saved from death. While an accurate examination of the
intensity of the jaundice condition can be determined by a measurement of
the bilirubin value of the blood serum taken from newborns, it can be
rather difficult or is often even unnecessary to take blood from each and
every newborn for this measurement. Generally, doctors have made a visual
observation of the color of the newborn's skin and then decided if there
was any necessity to take a blood specimen for measurement of the
bilirubin value of the blood serum.
To assist the doctors in making this visual observation the Gosset
Icterometer has been developed and is employed as a screening test for
deciding whether there is a need to test the bilirubin value of the blood
serum. Basically, the Gosset Icterometer utilizes a plurality of standard
color strips that are pressed against the skin of the baby and visually
matched. Problems existed, however, due to the spectral reflection factors
of the yellowish reference strips on the Icterometer, particularly under
artificial illumination. Accordingly, although the prior art Icterometer
has been of great assistance to the medical profession as a preliminary
screening method, it frequently was necessary to rely upon the actual
measurements of bilirubin in the blood serum from simply a safety point of
view. Thus, quite frequently there are occasions of drawing blood from
newborns that are in good health.
Of interest to the present invention is the work of Ballowitz and Avery,
"Spectral Reflectance of the Skin", Biol. Neonate 15: 348-360 (1970) and
U.S. Pat. No. 4,029,085. Cited of general interest are several patent
disclosures relating to oximeters such as U.S. Pat. No. 3,638,640; U.S.
Pat. No. 3,677,648; U.S. Pat. No. 3,814,081 and U.S. Pat. No. 3,998,550.
Accordingly, there is still a demand in the prior art to provide a safe and
reliable objective test to determine the degree of jaundice in newborn
babies.
SUMMARY OF THE INVENTION
An electro-optical medical instrument for determining, from an objective
viewpoint, the degree, if any, of jaundice in a newborn baby is provided.
A light source capable of providing a pair of wavelengths of light having
approximately the same absorption coefficients with respect to hemoglobin
is used in one embodiment of the present invention. Preferably, the light
emitted from the light source has a sufficient quantity of light at a
wavelength at or below the maximum wavelength of bilirubin absorption
which is in the vicinity 455 m.mu.. In a preferred embodiment of the
present invention, the light source produces predetermined flashes of
light and utilizes integration circuits and sample hold circuits between a
photoelectric converting member and amplifiers. A pair of electrical
signals is produced with respect to two separate wavelengths of light and
these signals are processed by appropriate circuit means to provide a
determination of the bilirubin value in the baby's tissue.
The embodiment of the invention that utilizes a flash source of light can
further incorporate a switch designed to be activated at a certain
pressure, for example, at a certain force against the baby's skin to
activate the light source. Since the intensity of the flash light decays
in an exponential function of time a circuit provides the capability of
measuring the length of the period of time between one of the two
wavelength signals reaching a predetermined level and the time when the
other signal reaches the predetermined level. The period of time is a
function of the bilirubin density of the hypodermic tissue.
The features of the present invention which are believed to be novel are
set forth with particularity in the appended claims. The present
invention, both as to its organization and manner of operation, together
with further objects and advantages thereof, may best be understood by
reference to the following description, taken in conjunction with the
accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a perspective view of a Gossett Icterometer;
FIG. 2 is a graph showing the relationship between the Gosset Icterometer
scale and the total bilirubin value in te blood serum;
FIG. 3 is a chart showing the spectral reflection characteristics of the
referenced color strips of the Gosset Icterometer together with the
spectral reflection characteristics of the bilirubin;
FIG. 4 is a block diagram of one preferred embodiment of the present
invention;
FIG. 5 is a schematic cross-sectional view of an exemplary skin tissue;
FIG. 6 is a perspective view of another embodiment of the present
invention;
FIG. 7 is an exploded perspective view of an optical system for the
embodiment of FIG. 6;
FIG. 8 is a block diagram of the electrical circuit in the embodiment of
FIG. 6;
FIG. 9 is a timing diagram of voltage versus time length signals of the
embodiment of FIG. 6;
FIG. 10 is a circuit diagram of still another embodiment of the present
invention;
FIG. 11 is a partial circuit diagram of a modification to the embodiment of
FIG. 10;
FIG. 12 is a timing diagram relating to the embodiment of FIG. 10, and
FIG. 13 is a cross-sectional view of a switching mechanism.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
The following description is provided to enable any person skilled in the
medical field to make and use the invention and sets forth the best modes
contemplated by the inventor of carrying out his invention. Various
modifications, however, will remain readily apparent to those skilled in
this field since the generic principles of the present invention have been
defined herein specifically to provide a relatively economical and easily
manufactured medical instrument for determining jaundice in newborn
babies.
Referring to FIG. 1, the prior art Gosset Icterometer is disclosed in a
perspective view. Basically, this device comprises a transparent base
member supporting a plurality of strips with yellowish reference colors
and different color tones extending across the width of the base member.
These color reference strips are labeled No. 1 through No. 5 and are
spaced along the longitudinal axis to permit alternative transparent
portions to exist between two adjacent reference color strips. The doctor
would take the icterometer and press it against the nose of a newborn
child so that the flesh would be seen through the transparent strips. The
underlying blood in the tissue of the nose would be scattered by the
exerted pressure to reveal the original color of the skin. The doctor
would then compare the color of the pressed skin with the respective
yellowish reference color strips as an index and attempt to determine the
closest identifying number of the yellowish reference color strips to that
of the actual color of the skin.
The value obtained from the icterometer and the actual bilirubin value of
the blood serum of the child were correlated as indicated on the chart in
FIG. 2. This approach was practical because the unconjugated bilirubin is
fat soluble and accumulates to a large degree in the hypodermal tissue
which contains the greatest proportion of fat in the body of a newborn
child. However, as can be determined from the graph in FIG. 3, the
spectral reflection characteristics of the yellowish reference strips in
the icterometer differ from the actual reflection by bilirubin and
accordingly, a comparison of the skin color with the reference colors was
not accurate, particularly under artificial illumination and suffered from
variations relating to the subjective application of the test by either
the doctor or the nurse. As a result, a doctor would utilize the
icterometer test in a conservative manner to insure a sufficient safety
factor in determining the degree of jaundice in a newborn child.
The embodiments of the present invention which will be subsequently
described herein seek to remove the subjective determinations by
individual doctors with an objective standard which will permit a more
accurate determination of the condition of jaundice in a newborn child.
Additionally these purposes are accomplished with an apparatus that is
portable and capable of providing repetitive measurements with an
immediate visual display.
Referring to FIG. 4, a first embodiment of the present invention is
disclosed in a block diagram. Additionally, FIG. 5 schematically discloses
a cross-sectional view of skin tissue and its effect on light. Basically
light 1, emitted from a light source, finally reaches the hypodermic
tissue 4 of the skin after scattering, reflection and absorption by the
outer skin layer 2 and the actual or true skin tissue 3. As is well-known,
the hypodermic tissue 4 contains a large amount of fat especially in
newborn children so that the light 1 will have its shorter wavelengths
absorbed to a larger degree due to the bilirubin content in the hypodermic
fat. The light 1 reflected from the hypodermic tissue 4 again passes
through the true skin 3 and outer skin 2 after additional scattering and
reflection.
Although not shown in FIG. 4, it should be appreciated that a specific
light source for directing light into the skin and a specific conduit for
collecting light from the skin is utilized. The collected light is divided
into two components by a spectroscopic means such as a spectral beam
splitter 5. The splitter 5 provides at least a source of light with a
wavelength .lambda..sub.b (approximately 455 m.mu.) which permits a high
absorption coefficient by the bilirubin in the skin tissue and another
wavelength .lambda..sub.g (more than 500 m.mu.) wherein the absorption
coefficient of bilirubin in the skin tissue is low.
These two light components with different wavelengths are appropriately
sensed by photoelectric converting means such as a photoelectric
transducer 6 and 7 to produce a signal which is subsequently amplified by
amplifiers 8 and 9.
The outputs E.sub.b and E.sub.g of the amplifiers 8 and 9 can be
represented in the Lambert-Beer law as follows:
E.sub.b =A.sub.b .multidot.I.sub.o.lambda.b .multidot.F.sub..lambda.b
.multidot.e.sup.-a.sbsp.B.lambda.b.sup..multidot.C.sbsp.B.sup..multidot.d.
sbsp.B
E.sub.g =A.sub.g .multidot.I.sub.o.lambda.g .multidot.F.sub..lambda.g
.multidot.e.sup.-a.sbsp.B.lambda.g.sup..multidot.C.sbsp.B.sup..multidot.d.
sbsp.B
wherein
A.sub.b and A.sub.g are the coefficients of photoelectric conversion at the
wavelengths .lambda..sub.b and .lambda..sub.g (the product of the spectral
transmission factor of a filter, the sensitivity of the photosensitive
elements, the gain of the amplifiers, etc.);
I.sub.o.lambda.b and I.sub.o.lambda.g are the intensity of incident light
upon the skin of the wavelengths .lambda..sub.b and .lambda..sub.g ;
F.sub..lambda.b and F.sub..lambda.g are the attenuation in quantity of
light due to absorption, scattering and the reflection on the outer skin,
the true skin and the hypodermic tissue at the wavelengths .lambda..sub.b
and .lambda..sub.g ;
a.sub.B.lambda.b and a.sub.B.lambda.g are the absorption coefficients of
bilirubin at the wavelengths .lambda..sub.b and .lambda..sub.g ;
C.sub.B is the bilirubin density; and
d.sub.B is the equivalent light path length of bilirubin.
The resultant outputs E.sub.b and E.sub.g of the amplifiers 8 and 9 are
then subject to logarithm conversion by logarithm converters 10 and 11 and
subtraction by a subtractor circuit 12 in order to obtain ln (E.sub.b
/E.sub.g). If the coefficients A.sub.b and A.sub.g are adjusted to assure
A.sub.b .multidot.I.sub.o.lambda.b .multidot.F.sub..lambda.b =A.sub.g
.multidot.I.sub.o.lambda.g .multidot.F.sub..lambda.g (this can in fact be
accomplished by adjusting the gains of the amplifiers 6 and 7), then:
ln (E.sub.b /E.sub.g)=(a.sub.B.lambda.g -a.sub.B.lambda.b).multidot.C.sub.B
.multidot.d.sub.B
Since a.sub.B.lambda.b and a.sub.B.lambda.g are known values and d.sub.B
assumes substantially a fixed value inherent to a specific measuring
point, e.g., the forehead, the bilirubin density in the hypodermic tissue
can accordingly be evaluated through ln (E.sub.b /E.sub.g). The bilirubin
density is appropriately displayed on an indicator or display means 14 via
an amplifier 13.
It should be noted that human blood vessels are widely distributed in the
true skin 3 of FIG. 5 so that E.sub.b and E.sub.g may be under the
influence of absorption by the blood. To eliminate such influences of
absorption by the blood, the light outlet and light intake are disposed
very close to each other and the measurements are conducted under a
condition such that the blood is scattered out from the blood vessels in
the true skin to reduce the influences of absorption by blood to a
minimum. This can be accomplished by pressing strongly against the skin.
An electronic flash tube that can be appropriately timed for emission of
light, as subsequently described in FIGS. 6 and 7, can be used with the
embodiment of FIG. 4.
In addition, should the wavelengths .lambda..sub.b and .lambda..sub.g be
selected from within ranges of wavelengths corresponding to blue and green
light respectively, the absorption coefficients would be approximately
equal to each other with respect to hemoglobin so that the ratio of
E.sub.b to E.sub.g and hence the intended value of ln (E.sub.b /E.sub.g)
are free from any influences of the amount of blood. Therefore, even when
blood is incompletely removed from the tissue, it is still possible to
minimize an error in measurement.
The foregoing description is true when employing a source of constant light
such as a tungsten lamp. The quantity of light emission is, however,
critical since the maximum wavelength of bilirubin absorption is in the
vicinity of 455 m.mu. and the energy emitted from the tungsten lamp is
relatively weak in the short wavelength range whereas the sensitivity of a
silicon photocell is considerably low for short wavelength light.
Therefore, in a case where a light source such as the tungsten lamp or the
like is employed, it is necessary to insure the release of a significant
quantity of light. This, however, results unavoidably in a large-sized
lamp device and great inconvenience in measuring newborns in bed or the
nursing room. Accordingly, the present invention finds it desirable to use
an electronic flash tube such as a xenon flash tube which is of a
hand-held size and emits a satisfactory quantity of light in the desired
range per unit of time.
With this preferred embodiment of the invention, the light source produces
flashes of light and further requires integration circuits and sample hold
circuits between the photoelectric converting means 6 and 7 and the
amplifiers 8 and 9 respectively of the embodiment of FIG. 4.
In FIGS. 6 through 9, there is illustrated another embodiment of the
present invention. FIG. 6 shows, in a perspective view, an instrument
accommodated within a housing 15 of a pocket size, which includes a power
switch 16, a digital display panel 17 and a reset button 18. A holder 19
extends from both sides of the housing 15 and is movable upward and
downward relative to the housing 15 and is normally biased upwardly. A
light emitter or outlet is labeled 20 and the light intake is labeled 21.
FIG. 7 is an exploded perspective view of an optical system mounted within
the housing 15 of the above embodiment. Light released from the Xenon
flash tube 22 is guided to the light outlet 20 via a heat absorbing filter
23 and light source fiber guides 24 so as to impinge upon the skin at a
specific measuring point. The return light reaches the light intake 21
after suffering from intense absorption in the blue light wavelength range
due to the bilirubin contained within the hypodermic fat and then is
transmitted to a condenser lens 26 via fiber optic guides 24. Such
resulting light is divided into blue and green light components through a
dichroic mirror 27 and is received at light responsive elements 30 and 31
after passing through a blue filter 28 and a green filter 29,
respectively.
Prior to any measurements, the power switch 16 in FIG. 6 is turned on, the
reset button 18 is depressed and the light outlet 20 and the light intake
21 are pressed against the forehead of newborns while being grasped by
means of the holder 19. At this moment, the holder 19 is shifted downward
with respect to the housing 15 against a predetermined biasing force. When
the biasing force, which is equal to the pressure of forcing the light
outlet and intake 20 and 21 against the skin, becomes a predetermined
value of pressure, namely, when the holder 19 is shifted a predetermined
distance with respect to the housing 15, a trigger switch is automatically
closed for activation of the xenon flash tube 22 so that tube 22 releases
a flash of light for measuring purposes. Thus, the force of pressuring the
skin provides timing means for determining the firing of the flash. This
insures that the pressing force for scattering out blood is unchanged for
each measurement and further avoids any fear of applying too much pressure
to newborns. Therefore, the above embodiment is suitable for prompt
sequential measurements. Since the light outlet 20 and the light intake 21
pressed against the skin, the ambient illumination light is prevented from
entering into the light intake 21.
When it is desired to conduct measurements at a different physical point
such as the ear lobe, it may be sandwiched on both sides by the light
outlet and the light intake. In this case, the measurement device is of a
light transmission type.
FIG. 8 shows a block diagram of the signal processing from the light
receiving elements 30 and 31 to the indicator 40 for the FIG. 6
embodiment. The construction disclosed in FIG. 8 incorporates the
invention described in my copending U.S. patent application Ser. No.
16,561 filed Mar. 1, 1979 entitled "APPARATUS FOR OPTICALLY MEASURING A
PROPERTY OF AN OBJECT" assigned to the same assignee as this application.
The light source is provided by a source of flash light such as an
electronic flash tube of which the quantity of light emitted attenuates as
an exponential function of the passage of time. A value proportional to
the logarithm of a ratio of the outputs of the light receiving elements 30
and 31 is evaluated by measuring a period of time between two different
points in time; one point where the output of the light responsive element
30 reaches a predetermined level due to light attenuation and the other
point where the output of the light responsive element 31 reaches the
predetermined level. The output current of the light responsive element 30
is converted via a current-to-voltage converter 32 into an output voltage
which in turn is adjusted via again adjustment circuit 34 at the node 1
of FIG. 8. The output current of the light responsive element 31, on the
other hand, is converted into a corresponding output voltage via a
current-to-voltage converter 33 at the node 2 .
Since the manner wherein the quantity of light emission from the flash tube
attenuates is according to an exponential function of time, the output
voltages at the nodes 1 and 2 assume the following values at a
specific point, t, in time as long as a reference point in time is in
agreement with the emission rising edge and the quantity of light emission
begins to attenuate in the form of logarithmic function at t.sub.o
(wherein .tau. is the time constant):
##EQU1##
In the above defined formulas,
V.sub.ob =Ab.multidot.I.sub.o.lambda.b .multidot.F.sub..lambda.b
.multidot.e.sup.-a.sbsp.B.lambda.b.sup..multidot.C.sbsp.B.sup..multidot.d.
sbsp.B (3)
V.sub.og =A.sub.g.lambda. .multidot.I.sub.o.lambda.g
.multidot.F.sub..lambda.g
.multidot.e.sup.-a.sbsp.B.lambda.g.sup..multidot.C.sbsp.B.sup..multidot.d.
sbsp. (4)
Through gain adjustment, the following relationship is achieved:
A.sub.g.lambda. .multidot.I.sub.o.lambda.g .multidot.F.sub..lambda.g
=A.sub.b .multidot.I.sub.o.lambda.b .multidot.F.sub..lambda.b
The outputs at the nodes 1 and 2 are applied to comparators 35 and 36
for comparison with a reference voltage from a reference voltage generator
37. The output voltage of the comparator 35 (or 36) at the nodes 3 (or
4 ) is high when the voltages at the nodes 1 (or 2 ) is higher than
the reference voltage. Otherwise the output voltage is low. The voltage
waveforms appearing at the nodes 1 , 2 , 3 and 4 are depicted in a
timing diagram shown in FIG. 9.
If V.sub.c is the reference voltage and t.sub.b and t.sub.g are the points
in time wherein the voltages at the nodes 1 and 2 become equal to
V.sub.c, then
##STR1##
From the formulas (5) and (6),
##EQU2##
Therefore,
t.sub.g -t.sub.b =.tau..multidot.ln(V.sub.og /V.sub.ob) (8)
Considering formulas (3) and (4), the formula (8) can be rewritten as
follows:
t.sub.g -t.sub.b =.tau..multidot.(a.sub.B.lambda.b
-a.sub.B.lambda.g)C.sub.B .multidot.d.sub.B (9)
In FIG. 8, a counter 38 starts counting pulses from a clock pulse generator
39 at the point t.sub.b in time and discontinues counting at point t.sub.g
in time.
As a result, the number of pulses counted is proportional to (t.sub.g
-t.sub.b) and a value proportional to the value given in the formula (9)
can be evaluated. Since .tau., a.sub.B.lambda.b and a.sub.B.lambda.g are
already known and d.sub.B is substantially identical if measuring points,
e.g., foreheads, are identical it is thus possible to evaluate the value
proportional to the bilirubin density C.sub.B of the hypodermic tissue. To
evaluate the value directly indicative of C.sub.B, the cycle of the clock
pulses should be properly selected. A conventional means 41 is provided
for resetting the count of the counter to zero.
Considering the situation where the reference voltages V.sub.cg and
V.sub.cb of the comparators 35 and 36 are different, then,
##EQU3##
In the same manner as obtaining formula (9), the following formula is
obtained from formulas (10) and (11):
##EQU4##
If the following relationship exists in the above formula,
A.sub.g .multidot.I.sub.o.lambda.g .multidot.E.sub..lambda.g
.multidot.V.sub.cb =A.sub.b .multidot.I.sub.o.lambda.b
.multidot.E.sub..lambda.b .multidot.V.sub.cg (13)
then
t.sub.g -t.sub.b =.tau..multidot.(a.sub.B.lambda.b
-a.sub.B.lambda.g).multidot.C.sub.B .multidot.d.sub.B (14)
The formula (14) is identical with the above defined formula (9). When the
relationship as indicated by formula (13) exists in formula (12), (t.sub.g
-t.sub.b) should be zero with C.sub.B =0. This implies conversely that the
relationship as set forth in formula (13) can be fulfilled by adjusting
the gain so as to make (t.sub.g -T.sub.b)=0 when C.sub.B =0.
It is, therefore, not necessarily required that a discrete reference
voltage generator be provided to produce V.sub.c as the reference voltage.
The comparators 35 and 36 can be a pair of known Schmitt trigger circuits
for simplicity of circuit construction, which have V.sub.cg and V.sub.cb
of different reference levels, respectively.
FIG. 10 discloses still another embodiment of the present invention
constructed pursuant to the teachings of the embodiments of FIGS. 6
through 9. This embodiment includes a main switch S.sub.1 for supplying a
measurement and display system with power from V.sub.DD and enabling a
light source system ready for power supply, and a light source switch
S.sub.2. When the switch S.sub.2 is closed, a main capacitor C within a
charging circuit 43 is charged from a high voltage generator 42 of a
well-known direct current to direct current (D--D) converter construction.
Provided that a trigger switch, S.sub.3, in a trigger circuit 44 is closed
at the beginning of the measurements, a xenon flash tube T in a light
source section 45 consumes the charge accumulated on the main capacitor C
for light emission. A resistor R is provided in the light source section
for increasing the time constant as to the attenuation of the quantity of
light.
Through reflection from the skin tissue of newborns, the light from the
xenon flash tube T is incident upon a blue light responsive silicon
photocell P.sub.1 and a green light responsive silicon photocell P.sub.2
within a light receiving section 46.
The output of silicon photocells, P.sub.1 and P.sub.2, are connected
respectively to amplifiers within current-to-voltage converters 47. Each
of the amplifiers can be implemented by a well-known operational amplifier
OP.sub.1 and OP.sub.2. A potentiometer R.sub.v is further provided for
gain adjustment. A pair of Schmitt trigger circuits in block 48 are
connected to the outputs of the amplifiers to provide outputs which are
inverted according to the output levels of the amplifiers.
Two 4-bit counters 49 are provided in the order of units and tens of units
and the contents are displayed via a display circuit 50 comprising a
decoder driver and a seven-segment display element. The output pulses from
a clock pulse generator 53 are connected to the input E of the counter 49
in the order of units during the period of time where its gate terminal is
at low level.
A timing circuit 51 comprises a combination of conventional logic circuits
and delay circuits, and gates the gate terminal a of the counter 49. The
output terminal a thereof is low during a period between two points in
time; one point, wherein the output of one of the Schmitt trigger circuits
changes from high to low due to attenuation of the output of the blue
light responsive silicon photocell P.sub.1 and the other point wherein the
output of the other Schmitt trigger circuit changes from high to low due
to that of the green light responsive silicon photocell P.sub.2.
A reset circuit 52 is adapted to receive the output of the Schmitt trigger
circuit changeable in response to the output of the green light responsive
silicon photocell P.sub.2 and a signal developed when the main switch
S.sub.1 is closed. Upon closure of the main switch S.sub.1, the reset
circuit 52 receives the signal at V.sub.DD and provides a reset signal at
the output b. The reset signal is received at a reset terminal b of the
counter 49 to reset the count to zero. On the other hand, when the xenon
flash tube releases light and the output of the green light responsive
silicon photocell exceeds the value of a reference potential, the output
of the Schmitt trigger circuit changes from low to high so that the reset
circuit provides the reset signal at the output terminal b, again
resetting the count of the counter 49 to zero. Thus, before the output of
the Schmitt trigger changes from high to low to initiate the counting
operation due to attenuation of the output of the blue light responsive
silicon photocell, the previous count of the counter 49 is automatically
reset to zero and ready for a new measurement.
The above embodiment is suitable for prompt sequential measurements since
the results of the previous measurement are reset automatically at the
beginning of a new measurement without any particular reset operation. It
should also be noted that the present invention provides a portable
electrooptical medical instrument that can be held by hand and is
self-contained.
In FIG. 11, there is illustrated a further improvement in the amplifier
utilized within the current-to-voltage converter 47 of the embodiment of
FIG. 10, wherein a diode D is connected to the input of the operational
amplifier OP in parallel with the silicon photocell P.
The embodiment of FIG. 10, utilizing attenuation of the output of the
amplifier operates, in principle, successfully even when the peak value of
the output of the silicon photocell, P, is so high as to saturate the
amplifier and the output of the amplifier does not fully follow
transitions in the output of the silicon photocell. It is enough for the
amplifier to follow transitions in the output of the silicon photocell in
the output attenuation region necessary for measurements.
As a matter of fact, however, if the amplifier is in a saturated condition,
then the node a of FIG. 11, provided that diode D is not added, will not
be in the imaginary ground condition so that the potential falls and
excessive charge is accumulated on a phase-compensating capacitor Cf
within the amplifier.
The curve 1 in FIG. 12 shows variations in the output of the amplifier
when the power supply voltage to the amplifier is high enough not to
saturate the amplifier, whereas the curve 3 depicts variations in the
output of the amplifier caused by the influences of the charge accumulated
on the capacitor Cf in case that amplifier is saturated at V.sub.s. As a
consequence, the point t.sub.g, wherein the reference potential V.sub.cg
is reached is shifted to t.sub.g '.
However, in a case where a diode D is connected as indicated in FIG. 11,
the forward current is shunted through the diode D after the output
voltage is saturated so that the fall of potential at the node, a, is
prevented and the output waveform of the amplifier approaches the curve 1
as is obvious from curve 2 in FIG. 12. A high degree of accuracy is,
thus, assured even when the output voltage is saturated.
FIG. 13 shows a schematic connection between the trigger switch S.sub.3 in
FIG. 10 and the construction in FIG. 6. Holder 19, which is upward and
downward slidable relative to the housing 15, is normally biased toward
the upper side of the housing 15 by spring S.sub.p. If the housing 15,
held by the holder 19 is pressed against the skin of a newborn baby,
holder 19 will be moved against the force of spring S.sub.p, toward the
direction of the arrow relative to the housing 15, with the lower side of
the housing 15 kept in contact with the skin. When the holder 19 is
shifted a predetermined value relative to the housing 15, projection 19a
pushes a pair of contacts forming switch S.sub.3 to a closed position.
Thus, switch S.sub.3 is always closed when the pressure of the lower side
of the housing 15 on the skin reaches a predetermined value for actuating
the flash tube T of FIG. 10 to emit a measurement flash light source.
As stated above, the present invention provides a medical instrument which
performs measurements accurately, irrespective of differences in the
surrounding illumination light and different operators assure a high
degree of reliability in comparison with the prior art screening method.
In addition, the present invention both permits an early check of jaundice
which may endanger the life of newborns, while eliminating the need to
draw blood from newborns in good health.
While the above embodiments have been disclosed as the best mode presently
contemplated by the inventor it should be realized that these examples
should not be interpreted as limiting, because artisans skilled in this
field, once given the present teachings, can vary from these specific
embodiments. Accordingly, the scope of the present invention should be
determined solely from the following claims in which
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