 |
Description  |
|
|
BACKGROUND OF THE INVENTION
1. Field of the Invention
The present invention concerns a pulse measurement device. More
particularly, it concerns an improved, portable, wearable mechanism for
obtaining a relatively noise-free measurement of human pulse rate, under
conditions of motion or other activity that tends to create severe noise
in the signal. uch a device may be termed a "wristwatch pulsemeter."
2. Brief Discussion of the Prior Art
Several devices have been proposed for providing a wristwatch type of
pulsemeter. One type of such device is the digital plethysmograph
described in Prinz U.S. Pat. No. 4,120,296, which customarily utilizes an
infrared light transducer. Others have proposed using piezoelectric or
other pressure sensitive transducers, such as in Stupay U.S. Pat. No.
4,059,118, which uses an "actuator" pin pressing against a piezoelectric
crystal.
Typically, such devices tend to have several shortcomings. Those using an
optical transducer, such as the digital plethysmographs, consume
substantial power in their light-emitting elements, and thus use up their
battery life rapidly. Those devices suggesting use of piezoelectric
transducers, such as Stupay, typically devote little attention to the
substantial noise problem that attends use of such transducers in this
application.
When such a pulsemeter is mounted on the wearer's body, as in a wristwatch
device, the pulse signal is to a substantial extent masked by concurrent
noise signals due to body motions. The mechanical transducer responds both
to pressure from the wearer's pulse beat and to motion from walking, arm
swinging, and the like, and does not distinguish between them. The latter
is noise, however, insofar as pulse measurement is concerned. Thus, the
Stupay patent notes that "the patient must remain quiet to avoid noise
input" during the period in which the pulse rate is measured.
Also, if the piezoelectric transducer is not mounted directly over the
artery of the user, the pulse signal measured by such devices is of
considerably lessened amplitude, and is thus even more likely to be masked
by noise. Typically, noise signals may be as high as as 1.0 volts, while
the pulse signal may be approximately 0.1 volts. Prior art wristwatch
pulsemeters of the piezoelectric transducer type have been inaccurate
because of this very unfavorable signal-to-noise ratio. Thus, Cramer U.S.
Pat. No. 4,224,948 states that when a piezoelectric transducer is used,
"the watch must be worn on the volar surface of the wrist but lateral to
the tendon cord bundles," so as to obtain a pulse reading from the radial
artery in the subpollex depression; further, "the sensors must be forced
into the flesh of the wrist for a reading" and "[t]his situation may be
uncomfortable."
Insofar as the inventor is aware, the prior art does not disclose an
effective noise-free piezoelectric transducer mechanism for human or
animal pulse measurement, which obviates the difficulties described above.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 shows the wristwatch pulsemeter as viewed when in place on a user's
wrist, looking toward the inside of the wrist.
FIG. 2 is a plan view of the underside of the transducer case of the
wristwatch pulsemeter.
FIG. 3 is a side view of the case, showing the transducer pressed against
the user's wrist.
FIGS. 4A to 4H are cross-sectional side views of the transducer case,
showing various transducer configurations.
FIGS. 4J and 4K are details of the piezo-bender and post.
FIG. 5 is a cross-sectional view of the case with a pair of
differentially-connected transducers.
FIG. 6 is a plan view, in section, of the case of FIG. 5, as viewed from
underneath.
FIG. 7 is a flow chart for the differentially-connected transducer
wristwatch pulsemeter.
FIG. 8 is a perspective view of a five-transducer wristwatch pulsemeter.
FIG. 9 is a cross-sectional side view of the case of the device shown in
FIG. 8.
FIG. 10 is a flow chart for the five-transducer wristwatch pulsemeter of
FIG. 8.
BRIEF SUMMARY OF THE PRESENT INVENTION
The invention descried below is intended to lessen or obviate the problems
of noise and power consumption, by providing a low-energy-consuming
transducer arrangement that substantially eliminates extraneous noise. The
use of a piezoelectric element eliminates the power loss attendant to LED
and similar devices. The mounting means disclosed herein for the
piezoelectric element largely eliminates noise. Use of multiple transducer
arrays in which some transducers act as references even further reduces
noise, to the point where it is substantially eliminated. The resulting
device permits visual or other monitoring of pulse rate in a human or
animal body, on a consistent, error-free basis.
DETAILED DESCRIPTION
A perspective view of the simplest contemplated embodiment of the present
invention may be seen in FIG. 1, from a vantage point looking toward the
inside of a wrist 10 of a user of the device. A transducer housing or case
12 is fastened to a wrist band 14, surrounding the user's wrist and
fastened to a digital wristwatch product (containing microprocessor and
display). The wristwatch product to which band 14 is attached is not shown
in this view, and is concealed by wrist 10. Case 12 has a pair of
laterally projecting flanges 16 and 18, which function as a marking device
to facilitate the user's placement of band 14 so that the transducer (not
shown) within case 12 is placed directly over radial artery 20 of wrist
10. Another appropriate marking device can be used instead of flanges 16
and 18. In this embodiment of the invention, it is desirable to have the
transducer as close to directly over the wrist's radial artery as
possible, to maximize the signal-to-noise ratio. If the device is used to
monitor pulse in a different artery, e.g., one in the human or animal
user's leg, the transducer should be as close as possible to a position
directly over that artery.
In FIG. 2 the underside of transducer case 12 is shown in plan view. It may
be seen that between flanges 16 and 18 is a transducer pulse contact post
22, which is intended to be placed on the skin of the user as closely as
possible to directly over the radial artery, and biased against the skin
so that it moves in response to the pressure from pulse beats. Post 22 is
fastened to a piezoelectric bender transducer element ("piezo-bender") 24,
shown in dotted lines. (The mounting of piezo-bender 24 is shown in FIGS.
4A to 4H.) FIG. 3 shows a side view of case 12, in which post 22 projects
out from case 12 in the direction of the user's skin and radial artery.
Again, piezo-bender 24 is shown in dotted lines.
In FIGS. 4A to 4H, a series of cross-sectional views of transducer cases is
shown, with various different configurations for mechanically filtered
suspension and mounting of transducers, with which the applicant has
experimented. What may be termed a spring mounted dual cantilever
arrangement is shown in FIG. 4A. This has been found to be the most
advantageous arrangement, so far. In this configuration, post 22 is
cemented to piezo-bender 24 on the middle of one face or side (the "lower
side," i.e., that closer to the user's skin) thereof; Super Glue is an
effective cementing agent. The piezo-bender is elastically mounted to case
12 by means of a pair of upper springs 26 and 28 fastened to the
piezo-bender near the ends of the piezo-bender's other face or side (the
"upper side," i.e., that farther away from the user's skin). A perspective
view of post 22 and piezo-bender 24 is shown in detail in FIG. 4J.
Typically, piezo-bender 24 is about 0.5 inch long, 0.06 inch wide, and
0.02 inch thick. (The thickness of piezo-bender 24 is exaggerated in FIG.
4J to facilitate viewing.)
In ordinary operation of the device, as previously indicated, post 22
firmly contacts the skin of the user, above the radial artery. Springs 26
and 28 bias post 22 against the skin. The user's pulse beat presses post
22 upward against piezo-bender 24. Springs 26 and 28 resist the upward
motion of post 22, causing piezo-bender 24 to bend and flex, which results
in the generation of a signal. The resulting signal is delivered to a
microprocessor and display in the pulsemeter, as explained more fully
hereafter, via a pair of wires 58a-b soldered to piezo-bender 24, at
opposite corners of the piezo-bender "sandwich."
Springs 26 and 28 also act as a mechanical filter for the signal,
attenuating and largely eliminating frequencies not passed by the filter.
Selection of springs with appropriate physical constants (relatively
"soft" springs) permits attenuation of high frequency noise components of
the signal generated by piezo-bender 24 without undue loss of the lower
major pulse signal frequency components. In contrast, when piezo-bender 24
is suspended rigidly or by relatively "stiff" springs, the noise
components are passed and tend to have peaks of 1.0 volts or greater,
while pulse signal peaks are about 0.1 volts. Frequencies between 10 and
approximately 50 Hz are those of major use in this pulsemeter device, as
discussed more fully hereafter, while noise signals caused by body motion
and the like tend to be over about 50 Hz. It is therefore desirable to use
a low-pass ("soft") spring with a cut-off at about 50 Hz, to eliminate
noise due to motion.
In FIG. 4B, another dual cantilever configuration for suspension of
piezo-bender 24 is shown. In this configuration, foam pads 30 and 32
replace springs 26 and 28 of FIG. 4A, to anchor, cushion, and filter
piezo-bender 24. What may be termed a quadruple spring mounted dual
cantilever arrangement is shown in FIG. 4C. In this configuration upper
springs 26 and 28 of FIG. 4A are supplemented by a pair of lower springs
34 and 36, which connect the lower side of piezo-bender 24 to case 12 in
the same way that upper springs 26 and 28 connect the upper side of
piezo-bender 24 to case 12. In FIG. 4D, a pair of "rubberband" tension
elements 38 and 40 connect piezo-bender 24 to the lower inside of case 12.
These tension elements may also be springs. In all of the configurations
shown in FIGS. 4A to 4D, transducer post 22 is mounted to the middle of
piezo-bender 24 and the two ends of piezo-bender 24 are suspended with
elastic elements. The latter bias post 22 against the user's skin and also
filter out some of the higher frequency elements of the force signal
applied to the transducer, and of the output voltage signal that it wold
otherwise generate.
In FIGS. 4E to 4H, a series of lever mounted transducer configurations are
shown. In FIG. 4E, post 22 is fastened near one end of piezo-bender 24, on
its lower face, as shown also in detail in FIG. 4K. The other end of
piezo-bender 24 is cemented to a rubber mount 42, which is cemented to the
inside end of case 12. An upper spring 44 connects the middle of the upper
side of piezo-bender 24 to the inside of the top of case 12. In operation,
the user's pulse presses post 22 up against piezo-bender 24 against the
resistance of spring 44. Piezo-bender 24 flexes and generates a signal as
before. A perspective view of the piezo-bender as used in these
configurations is shown in FIG. 4K.
In FIG. 4F, piezo-bender 24 cantilevers out from foam pad 46, which is
cemented to the inside end of case 12. Post 22 projects down from the free
end of piezo-bender 24. In FIG. 4G, a pair of "rubberband" tension
elements 48 and 50 connect the lower side of piezo-bender 24 to case 12;
again, post 22 projects down from one end of piezo-bender 24. In FIG. 4H,
one end of piezo-bender 24 is fastened from below to the inside end of
case 12 by a lower spring 52. The middle of piezo-bender 24 is fastened
from above to the inside top of case 12 by an upper spring 54. From the
free end of piezo-bender 24, post 22 projects down. In all of the
configurations shown in FIGS. 4E to 4H, transducer post 22 is mounted to
one end of piezo-bender 24 and the other end of piezo-bender 24 is mounted
by an elastic element to the transducer case, so that post 22 is biased
against the user's skin. The elastic element also filters out some of the
undesired (noise) frequencies from the force signal applied to post 22 by
the user's pulsebeat.
The useful (non-noise) electrical signal from piezo-bender 24 is typically
of the order of magnitude of 0.05 to 0.15 volts. The lower figure is more
typical of "at rest" pulse beat, while the higher one is more typical of
exercise conditions. Signal magnitude also varies from person to person.
Although the repetition frequency of human pulse is on the order of
magnitude of 1 Hz, the leading edge of the signal tends to contain
frequencies on the order of 10 to 50 Hz. Such frequency components are
those that the circuitry described hereafter is intended to process. The
signal may advantageously be electronically filtered, to further attenuate
over-50 Hz noise frequencies, and this signal may be further processed and
used as the input to conventional microprocessor circuitry of the digital
watch type. It has been found advantageous to use the filtered pulse
signal to drive a standard Schmitt Trigger or a comparator, so that a
digital-compatible signal is derived from the pulse beat's analog signal,
in order to provide an appropriate input for the microprocessor.
The pulsemeter microprocessor's output may be displayed on a conventional
visual display of the digital watch type. Because the microprocessor and
its display are substantially that which is used in a conventional digital
watch, the present invention may be advantageously used in connection with
such watches, as an additional optional feature thereof. Pulsemeter output
may also be monitored acoustically or may be monitored by being sampled
and stored in a memory device (such as a random access memory ("RAM"), for
subsequent analysis. The latter permits observation of a patient's pulse
for presence of arrhythmias, over a long period and away from the
physician's office.
A more advanced embodiment of the invention is shown in FIG. 5. Here, a
pair of piezo-benders 24a and 24b is used. Both are elastically mounted,
side by side, but staggered, less than 0.015 inches apart, in a
configuration similar to that shown in FIG. 4A, by means of springs 26a,
26b, 28a, and 28b. (The piezo-benders are each shown tipped to one end, in
FIG. 5, so that the farther one may be viewed.) Two pairs of signal wires
58a-58b and 60a-60b carry the output signals from piezo-benders 24a and
24b to the electronic circuitry, described hereafter. The wires may
advantageously be twisted, to lessen noise pickup, and they exit the
transducer case through a tightly grommetted aperture, and pass along the
watchband to the electronic circuitry described below, which may
advantageously be housed in the watch case. In FIG. 6, a view of the
underside of the transducer case is shown in cutaway view, showing the
staggered, side-by-side arrangement of the two transducers of FIG. 5, and
their respective posts 22a and 22b. As previously indicated, the
piezo-benders are approximately 0.5 inch long and 0.06 inch wide.
Post 22a of piezo-bender 24a is placed over radial artery 20, as in the
device shown in FIG. 3. Nearby, post 22b of piezo-bender 24b senses
substantially the same noise due to motion and the like as does post 22a,
but the force of the pulse signal from artery 20 is greatly attenuated at
post 22b. An advantageous alternative arrangement of the transducers is
shown in FIG. 7. Instead of staggering the transducers longitudinally in
order to laterally separate posts 22a and 22b relative to the longitudinal
axis of the radial artery, as in FIGS. 5 and 6, this arrangement rotates
the transducers in the case by 90 degrees, so that the longitudinal axis
of the transducers is now parallel to the longitudinal axis of the radial
artery. Consequently, posts 22a and 22b are now laterally separated
relative to the longitudinal axis of the radial artery, without need for
staggering them. (A similar arrangement for five transducers is shown in
FIG. 9. )
Representations of the resulting voltage signals from the two piezo-benders
are shown in FIG. 7 as A and B, where A is the voltage signal from the
transducer over the radial artery and B is that from the nearby (noise
reference) transducer. FIG. 7 further depicts (in flow chart form) the
processing of these two signals to produce a visual pulsemeter display.
Signals A and B initially both have considerable noise. Much of the noise
can be eliminated by an active filtering and amplification stage. Thus,
signals A and B are respectively routed through low-pass
filter-amplification stages 62a and 62b. The filtered and amplified
signals A and B, with components over about 50 Hz largely eliminated, are
fed to differential amplifier stage 64.
Almost all of the remaining noise of all frequencies is subtracted out by
differential amplifier 64. Voltage signal A may be represented as:
A=K.sub.1 (S+N), where K.sub.1 is a constant associated with the first
transducer and amplifier input, S is a radial pulse force signal, and N is
the noise force signal due to motion and the like. Similarly, voltage
signal B may be represented as: B=K.sub.2 (cS+N), where K.sub.2 is an
amplification constant associated with the second transducer and amplifier
input, and c is the attenuation factor constant for the second pulse
signal, because the second transducer is not directly over the radial
artery. If K.sub.1 and K.sub.2 are approximately equal, the signal
delivered from differential amplifier 64 is approximately K(A-B). Matching
the piezo-benders is believed to be the best way to insure that K.sub.1 is
approximately equal to K.sub.2, if the supplier's tolerances are not
deemed tight enough (approximately 10% or better). Another way is to
balance the two inputs to differential amplifier 64, but this is believed
to be a more costly procedure, and is therefore less preferred.
The signal output from amplifier 64 is then routed to an analog-to-digital
buffer stage 66, which converts the analog pulse output signal from stage
64 to a digital-compatible signal suitable as an input for a digital watch
microprocessor. This conversion may advantageously be effected with a
conventional Schmitt Trigger or comparator circuit. The resulting
digital-compatible signal is routed to pulse logic and microprocessor
stage 68, which converts the analog pulse signal by conventional means to
a digital signal representing, as a decimal number, the number of pulse
beats per minute that the user's heart delivers to radial artery 20. This
number is then displayed on visual display 70. (If acoustic display or
other monitoring is desired, different conventional circuitry may be used
therefor.)
A further embodiment of the invention is shown in FIG. 8. A five-transducer
array 72 is used, to make it unnecessary for the user to place the device
carefully over the radial artery. Again, the transducer configuration of
FIG. 4A is preferred. FIG. 9 shows a sectional view of the transducer case
12, with the five-transducer array 72. The array comprises five posts 22a
to 22e, fastened to five piezo-benders 24a to 24e, and elastically
suspended by springs or elastic suspension elements 26a to 26e (which are
shown in FIG. 9, and elastic suspension elements 28a to 28e which are not
shown in FIG. 9). In FIG. 9, post 22b is over the radial artery, and thus
picks up the maximal pulse signal. The transducers are arrayed side by
side. They are approximately 0.05 inches wide and are spaced about 0.05
inches apart.
In FIG. 10, a flow chart for the signals of array 72 is shown. The five
transducers produce signals A, B, C, D, and E. Each signal is fed to a
low-pass active filter and amplification stage, 74a to 74e. The resulting
output signals are then passed to a signal averaging stage. Signals A and
C are fed to a signal averager 76, which sums inputs A and C and outputs
0.5(A+C). Similarly, averager 77 outputs 0.5(B+D) and averager 78 outputs
0.5(C+E). These averaged signals are then fed to a set of differential
amplifiers to permit subtraction of an averaged noise signal from a
noise-plus-pulse signal.
The inputs to differential amplifier 80 are B and 0.5(A+C), and the output
is B-0.5(A+C). Thus, this signal is the voltage produced by the pulsebeat
signal delivered to transducer post 22b, with noise superimposed on the
signal, minus the average of the voltage signal produced by motion at the
two adjacent posts 22a and 22c. This average is substantially the same as
the noise superimposed on pulsebeat signal B. Similarly, differential
amplifiers 82 and 84 produce respective outputs of C-0.5(B+D) and
D-0.5(C+E). The arrangement of FIG. 10 therefore produces three possible
signals, each of which has the average of the two nearest noise signals
subtracted from it. The resulting outputs are fed to logic and
microprocessor circuit 86, which selects a pulse signal (here, signal B)
and processes it by conventional means into a signal for digital display
70 to show as a numerical representation of the user's pulse rate. The
selection is advantageously performed by passing each differential
amplifier output signal to a Schmitt Trigger circuit, or a comparator,
which amplifies and passes only that signal of sufficient amplitude as
exceeds a predetermined threshold value (e.g., equivalent to a 0.04 volt
transducer signal). The output of the comparator is adjusted to be at the
0/1 levels required by the digital watch microprocessor.
This arrangement contemplates that one of the three middle transducer posts
(22b, 22c, or 22d) will be over the radial artery. If it were contemplated
that the extreme end transducer posts (22a and 22e) might also at times be
over the radial artery, slightly modified circuitry could be used to
provide, also, signals of A or E, minus the average signal of the two
nearest transducers, or simply A or E, minus the nearest transducer's
signal (B or D, respectively). Analog circuitry was used at this point
rather than digital circuitry, but the same kind of result could be
obtained by digital means. It may be thought that with this configuration,
the radial artery might fall exactly halfway between two transducer posts,
e.g., 22b and 22c. It might be thought that the result could be that no
pulse could be read. This is not the case, however, in the circuit
disclosed here. First, it has not been observed that the device will
remain in a position with the radial artery halfway between two transducer
posts. The natural notches and grooves of the human wrist appear to cause
one of the posts to settle into a depression over the radial artery and to
resist being dislodged. Consequently, two posts do not ordinarily rest in
locations where both of them pick up a strong pulse signal. In any case,
even when two somewhat attenuated pulse signals are fed through the
system, there is enough gain available to operate the microprocessor, and
there are no double counts or missed counts. The microprocessor input can
be fed a substantially squared or flat wave (0/1 voltage level), rather
than a pulse, so that if two comparators present overlapping inputs to the
microprocessor it counts them as one input.
In the preferred form of this embodiment, as now contemplated, the array of
five transducers is in a straight line along the circumference of the
user's wrist. The transducers could be staggered in a zig-zag array
without adversely affecting the operation of the device. Other such
arrangements are also possible, for example, a pentagonal or hexagonal
array. It is also possible to use the average of all other transducers as
a noise reference, rather than simply the two nearest ones.
More generally, this embodiment contemplates the use of an array comprising
a number of transducers. The extreme ends of the array (a and e of FIGS. 8
to 10) are not intended to be placed over the radial artery in operation
of the pulsemeter; they are merely present for noise reference purposes.
The other transducers in the array may or may not be over the radial
artery, depending on how the wristband is placed; only one of these
transducers will be directly over the radial artery or closest to the
artery. Those transducers that can occupy a position over or near the
user's radial artery (b, c, and d of FIGS. 8 to 10) may be termed
"potential sensors." The transducer actually closest to the user's radial
artery at any particular time, and thus that with the signal of greatest
amplitude, may be termed the "actual sensor." The transducers other than
the actual sensor, at any particular time, may be termed "non-sensors."
Different members of the array of transducers (different potential
sensors) will act as the actual sensor if the wrist band is moved or put
on the user's wrist differently. One or more of the non-sensors may be
used as noise reference. When the average signal obtained from the one or
more non-sensors is subtracted from the signal of the sensor, a relatively
noise-free pulse signal is obtained. (The average signal of only one
non-sensor, as in the embodiment shown in FIGS. 5-7, is the signal of that
one transducer.)
EXAMPLE 1
A one transducer pulsemeter was made in accordance with the configuration
indicated in FIGS. 2, 3, and 4A. Springs were selected (Associated Spring,
Compression Spring No. C0057-006-0250-M) that effectively filtered out
force signals over 50 Hz. The piezo-bender was a Model R0505, Gulton
Industries, Inc., PZT ceramic piezoelectric bender. Stainless steel
insulated lead wires were soldered to the aluminized surfaces of the
piezo-bender at opposite corners of the "sandwich," and were then threaded
along the watchband to the watch case, as a twisted pair. Peak transducer
signals of approximately 0.2 volts and 0.15 second duration were observed,
which were fed (after filtering, low-pass 50 Hz) to an amplifier and
Schmitt Trigger. The output was then fed to a conventional digital watch
type of CMOS chip microprocessor (Motorola MC 146805E2) and conventional
4-digit LCD display. The single-transducer product was tested under
exercise conditions and gave repeatable and relatively noise-free
readings, when the user was at rest or while he was walking, and when the
device was tapped on. It was inaccurate, however, about half the time when
the user swung his arms, jogged in place, or jogged in linear motion.
EXAMPLE 2
A dual transducer pulsemeter was made in accordance with the configuration
indicated in FIG. 7. The piezo-benders were the same Gulton models, with
similar springs and stainless steel leads. The piezo-bender pairs used
were matched to within 5%. The low-pass filter-amplification stages 62a-b
of FIG. 7 were the two halves of a Linear Design LM082 8-pin dual
operational amplifier ("op amp"). Differential amplifier 64 of FIG. 7 was
half of another LM082 op amp, while buffer 66 of FIG. 7 was the other
half, connected as a Schmitt Trigger. The same microprocessor chip was
used.
The product was tested under exercise conditions and gave highly repeatable
and noise-free readings, when the device was aligned at or near the radial
artery. That is, it was accurate for each of the test conditions referred
to in Example 1, including jogging and arm-swinging. But this model can
become disaligned in use, which can cause inaccuracy.
EXAMPLE 3
A pulsemeter was made in accordance with the configuration shown in FIGS.
8, 9, and 10. Again, the same model of piezo-bender was used. Three 14-pin
Linear Design LM084 quad bi-FET op amps were used for the electronic
circuitry, providing up to 12 op amp stages. Five stages were used for
filtering and amplification elements 74a-e of FIG. 10; three, for
averagers 76, 77, and 78; and three, for differential amplifiers 80, 82,
and 84.
Similar tests were performed on the product, with similar results. The
device was moved, on the user's wrist, from time to time, in order to
disarrange the transducer array. Consistent results were nonetheless
obtained. Alignment with respect to the radial artery was unnecessary.
Readings under exercise conditions were substantially free of noise. That
is, jogging and arm-swinging did not cause inaccuracy.
It will thus be seen that the objects set forth above, among those made
apparent from the preceding description, are efficiently attained. Since
certain changes may be made in carrying out the above methods, and in the
constructions set forth, without departing from the spirit and scope of
the present invention, it is intended that all matter contained in the
above description and shown in the accompanying drawings shall be
interpreted as illustrative and not restrictive.
It is also to be understood that the following claims are intended to cover
all of the generic and specific features of the invention which, as a
matter of language, might be said to fall therebetween.
* * * * *
|
|
|
