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`Aug. 28, 1962
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`Filed Oct. 14. 1959
`
`A.
`D.KOMPEUEN
`APPARATUS FOR AUTOMATICALLY MEASURING BLOOD
`PRESSURE AND PULSE RATE
`
`3,051
`
`,
`
`165
`
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`|PR2018—01093
`
`Apple Inc. Ex. 1006 Page 1
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`IPR2018-01093
`Apple Inc. Ex. 1006 Page 1
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`
`
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`

`

`Aug. 23, 1962
`
`A. D. KOMPELIEN
`APPARATUS FOR AUTOMATICALLY MEASURING BLOOD
`PRESSURE AND PULSE RATE
`
`3,051,165
`
`Filed Oct. 14. 1959
`
`2 Sheets-Sheet 2
`
`
`
`DIASTOLIC POINT-
`DIASTOLIC AMPLIFIER
`CEASES OPERATION
`
`TYPICAL AV TRIGGERING
`
`DIASTOLIC AMPLIFIER
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`SYSTOUC POINT_
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`SYSTOLICAMPLIFIER
`zozoxoxozozoxoxoxoz:
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`PRESSURE AND VOLTAGE VARIATION ON TRANSDUCER
`
`CYCLE MOTOR RUN TIME
`
`PULSE RATE
`
`—V////////////////////////////////A
`
`DIASTOLIC BLOOD PRESSURE ._
`
`SYSTOLIC BLOOD PRESSURE
`
`'
`
`.
`
`.
`
`—V//////////////////m
`
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`
`PROGRAM SWITCHES 40 a 59 >10331.332.31.33319301033333333?
`
`RESET SWITCH 60
`
`0 IO 20 30 40 so so 70 so 90'IOO IIO
`SECONDS
`
`,
`
`PROGRAM CYCLE
`I:I INDICATES INTERVAL
`DURING WHICH FUNCTION F' 4
`'3 35"“ TAKEN
`1?”
`m INDICATES INTERVAL DURING
`WHICH READOUT MAY OCCUR
`XXX SWITCHES 4O, 59, a 60 CLOSED
`
`INVENTOR.
`ARLON D. KOMPELIEN
`f
`-A 7' ORA/EY
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`‘ W‘Wf’l‘
`
`|PR2018—01093
`
`Apple InC. Ex. 1006 Page 2
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`IPR2018-01093
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`

`

`w
`United States Patent Office
`3,®5l,lfi5j
`Patented Aug. 28, 1962
`
`1
`
`3,051,165
`APPARATUS FOR AUTOMATICALLY MEASURING
`BLOOD PRESSURE AND PULSE RATE
`Arlon D. Kompelien, Richfield, Minn., assignor to Minne-
`apolis-Honeywell Regulator Company, Minneapolis,
`'
`., a corporation of Delaware
`Filed Oct. 14, 1959, Ser. No. 846,468
`10 Claims.
`(Cl. 128—105)
`
`u
`
`My invention relates to apparatus for sensing and
`recording blood pressure and pulse rate and more par-
`ticularly to an improved apparatus for automatically
`sensing such physical functions on a human being.
`Medical apparatus which performs sensing and record-
`ing functions automatically and simply has become of
`increased importance as a means for replacing the man-
`ual operations performed by those working in the med-
`ical field in connection with operative and post-operative
`patient care and in connection with research of a med-
`ical nature.
`Increased accuracy and repeatability of
`measurement are significant both from a research stand-
`point and from the operational standpoint of modern
`hospital facilities. The present invention is directed to
`a photoelectric pneumatic process of sensing the human
`function of diastolic and systolic blood pressure and
`pulse rate in an improved automatic apparatus which
`provides for extreme accuracy of reading or measurement
`and continuing records relative to patient care.
`In the
`research field, physical body functions are being ex-
`amined in the field of aviation or avionics and continuous
`records of the physical characteristics of patients or sub-
`jects of research investigation .are becoming essential.
`The photoelectric method of detecting the presence of
`blood in a portion of the human body has been previ-
`ously utilized in connection with ox gen analysis of
`blood and has also been utilized in connection with the
`measurement of blood pressure. The present apparatus
`permits rapid and numerous measurements of these body
`functions accurately and rapidly with a continuous indi-
`cation and record of these functions without requiring
`any manual operation.
`It is therefore an object of this
`invention to provide an improved electrical apparatus for
`automatically sensing and recording a plurality of body
`functions.
`It is further an object of this invention to
`provide an improved electrical apparatus for the meas-
`urement of the physical function of systolic and diastolic
`blood pressure.
`Another object of this invention is to provide an im-
`proved apparatus for measuring blood pressure which
`performs the measurement of a rise in cuff pressure. A
`still further object of this invention is to provide an im-
`proved apparatus of this type which permits rapid meas-
`urement of blood pressure and pulse rate in a continu-
`ous sequence Without efiecting physical response or dis-
`comfort of the body to which it is applied. These and
`other objects of this invention will become apparent
`from a reading of the attached description together with
`the drawings wherein:
`FIGURE 1
`is a schematic drawing of the improved
`apparatus,
`
`FIGURE 2 is a diagrammatic view of an ear cuff used
`in the improved measurement apparatus,
`FIGURE 3 is a graph relating pressure to electrical
`response in the apparatus, and
`FIGURE 4 is a graph indicating the on .and off periods
`for the switching circuitry of the programming portion
`of the apparatus.
`One of the most variable and difficult to measure of
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`30
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`all human functions with repeatability of results and
`accuracy is that of blood pressure. While accuracy and
`measurement may be obtained through arterial punc-
`tures, this method is normally not feasible in patient care.
`The sphygmomanometer or arm cult which is used in
`the measurement of blood pressure on human beings is
`further not a feasible apparatus for the continuous meas-
`urement of blood pressure because of inaccuracies caused
`by the effect of continuous pressure on the portion of
`the body to which it is applied. The present apparatus
`utilizes an ear piece or cuff in which a light source photo-
`cell combination or photoelectric pickup is utilized to
`determine the amount of light transmitted through the
`tissue of the ear as a means for determining blood con-
`tent of the organ and hence the effect of pressure on the
`same. This approach and apparatus were basically used
`in connection with studies of oxygen content and blood
`and has also been used in connection with measurement
`of blood pressure in medical research. However the
`approach utilized to date has not provided for continu-
`ous and automatic measurement of blood pressure.
`Therefore the arrangement and apparatus for performing
`this automatic measurement is the subject of the present
`invention.
`The ear piece as shown in FIGURE 2 includes basi-
`cally a two part structure indicated generally at 10 as
`including a first part ll: having a cylindrical member 12
`mounted thereon and the upstanding portion 13 to which
`the second part 15 of the ear piece is connected and
`pivoted. The cylindrical portion 12 includes a light
`source indicated schematically in FIGURE 1 at 18 and
`an expansible chamber or pressure member 20 which
`chamber has a transparent surface 19 such that the light
`may be directed therethrough. The part 15 mounts
`thereon a photocell 25 so associated that the parts 15
`and 11 may be pivoted together with a portion of the
`ear positioned therebetween and clamped in this relation-
`ship such that pressure may be applied to the chamber
`20 and allowing expansion of the extremity of the cham-
`ber against the ear lobe forcing it against the piece 15
`in which this photocell 25 is located forcing blood from
`the ear therebetween. A pin or locking mechanism on
`the ear piece (not shown) prevents the device from open;
`ing when pressure is applied to the chamber 29.
`In this
`position the light and photocell are directly in line and
`enough space exists between these parts so that there is
`no pressure applied to the ear in addition to that of the
`bellows.
`
`Variation in opacity of the ear or portion of the body
`to which the ear piece is applied is caused by variation
`of blood content of the same to provide a varying amount
`of light from the source to the photocell to produce a
`signal output. With the transducer or ear piece on the ear
`and no pressure applied to the bellows the blood content
`in the ear or the capillaries pulses with normal blood
`flow causing the photocell to put out an alternating cur.
`rent type signal. As pressure in the bellows is slowly
`increased the alternating current signal from the photo-
`cell increases and reaches a maximum. This is caused
`by the pressure in the bellows forcing much of the blood
`from the ear except during a period when the blood is
`forced during heart pumping operation back through the
`capillaries. The pressure in the belllows corresponding
`to this point where the photocell signal is a maximum is
`the diastolic blood pressure. This signal is maximum since
`the pressure of the bellows is just able to squeeze out the
`blood in the capillaries at the minimum part of the blood
`pulsing pressure allowing the greatest chafigeRiéolifigt01093
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`3,051,165
`
`3
`variations. As pressure in the chamber is increased still
`further,
`the signal decreases and approaches zero level
`indicating the least opacity or variation in density. The
`point where the pressure drops to zero is the systolic pres-
`sure point since the maximum part of the pulsing blood
`pressure just reaches a point where it can no longer push
`- blood through the pressurized portion of the ear to vary
`the light of the photocell and hence the density of the ear
`remains uniform.
`The apparatus for automatically measuring these func-
`tions in addition to the ear piece 10 includes an air source
`for varying the air pressure applied to the ear piece. A
`conduit or pipe indicated at 36 has connected thereto a
`valve 31 to vent the conduit, a variable pressure reservoir
`32 operated by a cam 33 to vary the pressure in the con-
`duit, and a pressure to voltage transducer 34 connected in
`the conduit 3% with a connection leading to the pressure
`chamber 20 of the ear piece. Valve 31 is a solenoid op-
`erated valve which is energized through a switch 40 op-
`era-ted from a programmer 45. The programmer also
`operates the .cam 33 and other switches to be later identi-
`fied. A broken line connection in FIGURE 1 at 42, 43
`indicates the coupling to these switches.
`In addition, valve
`31 is operated by a second control switch 41 which, as
`will be later noted, is controlled by a time delay interval
`switch. The pneumatic or pressure portion of the ap-
`paratus is initiated with operation of the valve 31 to close
`the conduit which is normally vented to the atmosphere.
`Air is then trapped in the conduit 30 and chamber 32 such
`that .upon rotation of the cam 33 a pressure build up will
`be experienced in the chamber 20 of the ear piece to
`press against the ear causing the blood therein to be
`forced therefrom. The switch 40 or switch 41 will release
`or de-energize the valve 31 to allow the air in the conduit
`to rapidly vent to the atmosphere for release of pressure
`on the ear. The pressure to voltage transducer 34 pro-
`vides an electrical signal output in accordance with the
`pressure in the chamber 20 of the ear piece, which signal
`will be indicative of the actual pressure applied to the
`portion of the ear. Programmer or master control 45
`is controllably energized from a power source through a
`switching means
`(not shown) and will operate con—
`tinuously for a given cycle to perform the blood pressure
`measurement and pulse measurement functions to be
`later described.
`- The photocell .25 of the ear piece is energized from a
`light source and will provide a variable signal output of
`the alternating current type which is connected through
`conductor means 48 to a preamplifier unit indicated in
`block form at 59. The details of the preamplifier together
`with the amplifiers and relays to be later defined are
`omitted herein for simplicity since they are conventional
`components. The output of the preamplifier section 50
`is coupled through a condenser indicated at 51 to a voltage
`limiting network which permits the passage or flow of
`signals of pulsed voltage output only when the succeeding
`voltage signal is larger than the preceding voltage signal.
`This network includes a condenser 52 and a rectifier or
`diode 53 connected through a limiting resistor 54 to the
`diastolic amplifier indicated in block form at 55 with a
`restoring resistor 56 connected to ground connection and
`having a diode 57 in parallel circuit therewith. A further
`resistor 58 is also connected to ground connection beyond
`the diode 53. With this circuit arrangement the capaCitor
`52 charges to the peak output voltage from the pream-
`plrfier 50 each time the signal is higher than any preceding
`one. No signal will flow through the resistor 58 when
`signals of lesser amplitude occur since diode 53 remains
`back biased by the voltage on capacitor 52 during the time
`of these signals. Hence the diastolic amplifier 55 will
`respond onlyto a signal larger than the preceding charge
`on the condenser 52. Diodes 57 and 53 limit direction of
`current flow through this network.
`Connected in parallel with the condenser 52 is a short-
`ingor reset switch 60 operated through a mechanical
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`connection of the step controller or programmer 45, the
`mechanical connection being schematically indicated at
`42. Diastolic amplifier 55 provides a pulsed output which
`controls a conventional relay mechanism 65 having a
`contact or switch 66 which controls or connects the pres-
`sure to voltage transducer 34 to a memory capacitor or
`condenser indicated at 70. The schematic diagram in
`FIGURE 1 shows an electrical connection 68 schematical-
`ly connecting the transducer 34 to the relay 65 to be con-
`trolled by the contacts '66 of the relay 65 and being con-
`nected through a conductor 72 and an interval switch con-
`tact 75, to be later defined, to the memory capacitor 70.
`The output of the memory capacitor 70 controls the en-
`ergization of a diastolic memory amplifier 80 which re-
`sponds to the charge on the condenser 70 to provide a
`signal output to a recorder indicated generally at 100. A
`read-out switch mechanism 85 is included in the output
`connection from the amplifier 80 to the recorder 100 to
`selectively connect the output of the amplifier 80 to the
`recorder. This read-out switch, as shown by the me-
`chanical connection 42,
`is operated by the programmer
`45 or as a part of the same.
`It should be recognized,
`however, that this portion of the apparatus may be in-
`cluded in the recorder drive to sequence with the opera-
`tion of the programmer 45. A parallel circuit from the
`preamplifier 50 and coupling condenser 51' includes a
`conductor or electrical connection 90 and a limiting re-
`sistor 91 connected to a systolic amplifier indicated in
`block form at 95 whose output controls the operation of
`a pulsing relay 96 having a contact or switch 97 connecting
`the output of the pressure to voltage transducer 34 through
`the conductors or connection indicated at 99 to a circuit
`including an interval switch 101 and a memory capacitor
`102. The output of the memory capacitor controls the
`energization of a systolic memory amplifier 104 whose
`output is coupled to the recorder 100 through a read-out
`The read-out switch ‘105 like
`, switch indicated at 105.
`switch 85 may be operated through the mechanical con-
`nection 42 from the programmer or be included in the
`recorder.
`Also connected to the output of the diastolic amplifier
`is a stepping relay or switch 110 which is connected in an
`electrical circuit indicated at 111 through a contact 112
`of programmer 45 and a contact 114 of relay 65 controlled
`by diastolic amplifier 55, the stepping relay being opera-
`tively connected to actuate a resistance divider or signal-
`ling device 116 which is energized from a reference source
`117 to provide a signal output through a circuit "118 and
`a read-out switch 120 to the recorder 100. The stepping
`relay pulses with each pulse of output of the diastolic
`amplifier 55 to provide a stepping action which adjusts
`the wiper of the potentiometer type device or divider 116
`to provide a signal output in accordance with the number
`of pulses of relay 65. This will provide a voltage output
`in accordance with the number of blood pulses sensed by
`the photocell over a given time interval. The stepping
`relay 110 and resistance divider 116 act as an analogue
`converter to count and convert the number of pulses to
`an analogue signal output or a measure of the number of
`pulses sensed. An interval switch 131 of the time delay
`type which operates the contacts 75, 101, and 41, pre-
`viously indicated, is connected to and controlled by the
`operation of the relay 96 of the systolic amplifier 95
`through a contact 98 of the relay and connections indi-
`cated at 1138 and 139. A reset contact 59 for the interval
`switch is operated by the programmer 45 to insure that
`the interval switch will operate only during a period when
`measurements are being taken and will prevent extraneous
`signals from operating the switch after the systolic blood
`pressure measurement is taken until a new cycle of meas-
`urement has commenced. The contacts 112 connecting
`the stepping relay 110 to the pulse relay 65 of diastolic
`amplifier 55 are closed by the programmer 45 during the
`initial portion of the measurement cycle while reset con-
`tact 136 for the stepping relay “335310 1%ft8'1tbe9psplse
`
`70
`
`75
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`3,051,165
`
`5
`measurement period is complete, contact 112 opens and
`contact 136 closes to reset the stepping relay and the
`signalling device 116 back to the starting position for a
`new cycle of measurement.
`In addition, the time delay
`interval switch includes the switch contact 41 which is
`connected in a series circuit with switch 40 of programmer
`45 to control the energization of solenoid valve 31. Nor-
`mal blood flow in the ear without air pressure in the
`clamp of the ear piece is suflicient to produce a signal
`output from the photocell
`to periodically energize the
`systolic amplifier and keep the internal switch closed once
`it has been closed by contact 59. Since the programmer
`45 at the outset closes switch 59 pulling in interval switch
`131, the contact 41 will be closed at the outset of meas—
`urement. Contact 98 included in a time delay holding
`circuit (not shown) keeps interval switch 131 operated
`as long as it is not left unoperated for a period of over
`three or four seconds. With the series circuit for solenoid
`31 complete, the valve wil close, permitting a pressure
`build up in the clamp of the ear piece while contacts 75
`and 101 are also closed during the pulse measurement
`period and relays 65 and 96 are operating, read-out con-
`tacts 85 and 105 are open so that no blood pressure sig-
`nals reach the recorder.
`As indicated above, reset switch 60 which is operated
`by the programmer 45, operates to shunt condenser 52
`and under these conditions the diastolic amplifier 55 will
`respond directly to the pulsed output of the photocell.
`These conditions maintain during measurement of pulse
`rate and during this period the pressure source 32 does not
`alter the pressure in the chamber 20 of the ear piece sig—
`nificantly since contact 40 keeps the pressure system vented
`to the atmosphere. Following the measurement of pulse
`rate the programmer closes contact 40 and opens contacts
`60 and 59. The pressure in chamber 20 then increases
`to vary blood flow in the ear and the photocell 25 provides
`an increasing voltage output to the preamplifier 50. Dur-
`ing the pulse rate measurement period the contacts 59 and
`112 will be closed by the programmer and the interval
`switch 131 will remain energized, keeping contacts 41, 75
`and 101 closed. The reset contact 136 of the programmer
`will be open. During a larger portion of this time period
`the remaining contacts of the programmer will be open
`and no signals will be applied to the recorder. During
`this period the counting operation of the stepping relay,
`which is converted into an electrical analogue output,
`will provide a pulse count for the recorder which after a
`predetermined time period will be read out to the recorder
`through operation of switch 120. The interval switch
`which as indicated above is of the time delay type will
`remain closed between each pulse of signal output since
`the time delay circuit (shown in part) is being constantly
`reset through switch contact 98 of the systolic pulse relay.
`The interval switch had been initially energized and sus-
`tained in energization through contact 59 which is open
`at this time. Upon reaching the systolic blood pressure
`point,
`the signal output from the photocell will go to
`zero so the systolic relay will cease pulsing and the interval
`switch will open, dropping out contacts 41, 75 and 1011
`thereby isolating the memory capacitors 70 and 102 from
`the pressure to voltage transducer 34 and releasing or
`opening valve 31. During this period programmer 45
`will have also opened contact 59 so the interval switch
`can drop out. A contact in the interval switch (not
`shown) only allows contact 59 to re—energize it once
`it has dropped out.
`In this event should any extraneous
`signals be sensed by the amplifier 95 corresponding error
`voltages will not be placed on the memory capacitors be—
`fore they can be read out to the recorder. Prior to this
`time, the programmer will have opened switch 112 and
`closed switch 136. The latter switch establishes a reverse
`energization circuit through the structure of the stepping
`relay 110 which Will cause it
`to operate back to its
`original position. As indicated above, the amplifiers, pre-
`amplifier, relays and stepping relay together with the sig-
`
`6
`nal transducers are all of the conventional type and their
`details have been omitted for simplicity.
`In considering the operation of the apparatus refer-
`ence is made to the graph 4 showing the time sequence
`of operation of the switches associated with the program
`controller 45. It will be noted that valve ‘31 of the pressure
`source is initially energized through operation of switches
`40 and 41 to close the conduit to the atmosphere and
`seal the pneumatic system so that the cam may operate
`on the pressure bellows source 32 to raise the pressure
`in chamber 20. During this period the program reset
`switch 60 is closed for the pulse counting operation and
`the contact 112 of the programmer will be closed for
`operation of the stepping relay. The read-out switch 120
`wil-l be closed at the end portion of this period during
`which time it connects the count of the pulse rate from
`the potential signalling device 116 to the recorder. Dur-
`ing this period of time the cam 33 Will be so positioned
`that it will be opening the bellows of the pressure source
`and there will be no pressure in chamber 20 since valve
`31 is venting and the photocell output will be at the level
`indicated in the graph 3 of a small but uniform mag-
`nitude. As pressure is applied to the bellows 32 from
`the cam 33 the pressure in chamber 20 will
`increase
`when valve 31 is energized. At this portion, the reset
`switch 60 is open and the blood in the capillaries of the
`ear pulsing because of normal heart operation Will vary
`the optical density of the ear and hence the variation in
`light from the light source to the photocell to cause an
`increasing alternating current output. As the pressure
`is slowly increased by the bellows, the alternating cur-
`rent signal from the photocell increases and reaches a
`maximum pressure corresponding to the point of diastolic
`blood pressure. During this period of time the systolic
`and diastolic amplifiers 55 and 95 have been receiving
`a pulsed voltage output with increasing voltage pulses.
`The limiting network including the condenser 52 and
`rectifiers 53, 57 leading to the diastolic amplifier will
`respond only to increasing voltage pulses caused by the
`build up in pressure and the change in optical density
`in the ear as blood is forced out of the capillaries.
`It
`is during this period of time that the read-out switch
`120 is closed and the pulse rate signal is fed to the re-
`corder. As the diastolic and systolic amplifiers respond
`to varying voltage pulses, they operate the relays which
`connect through their switches the pressure to voltage
`transducer 34 to the memory capacitors 70 and 102.
`Each time one of the relays operates the pressure to
`voltage transducer is connected to the respective capac—
`itors. Since the diastolic relay makes its last pulse when
`the blood pressure is at the diastolic pressure point and
`the systolic relay makes its last pulse when the pressure
`in chamber 20 and hence on the transducer 34 is at the
`systolic pressure point the proper value can be left on
`the memory capacitors. The associated memory read-
`out amplifiers then feed the corresponding outputs to
`the recorder without discharging the capacitors.
`.As in-
`dicated by the graph in FIGURE 3 this diastolic pres-
`sure point is reached when the change in optical density
`in the ear and hence the photocell output reach a maxi-
`mum at which point the charge on the memory condenser
`70 will correspond to the pressure in the clamp of the
`ear piece. The continuing pressure applied from bellows
`32 acting as a pressure source will force more and more
`blood from the capillaries to a point where the pulsing
`blood Will not be able to enter the portion of the ear
`which is pressurized between the light source and photo-
`cell at which point the optical density variation will be
`at a minimum and the photocell output will be zero.
`However, at this point the voltage signal from the pres-
`sure transducer 34 will be at a maximum leaving the
`maximum charge on the condenser l1024. Slightly after
`these points, the switches 85, 105 respectively close to
`connect the outputs of the amplifiers 80, 104 to the re-
`ocrder, recording systolic and diastolic prifiufi28%;01 093
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`3,051,165
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`7
`The valve 31 is opened rapidly after the systolic point
`is reached through de-energization of interval switch 41
`and the switch 40 is also opened to exhaust the pressure
`chamber 20 and prevent any further pressure application
`to this car. The cam '36 also rotates towards its original
`position, releasing the bellows 32. The program selec-
`tor or controller rotates back to its original position to
`renew the sequence starting with the shorting of con-
`denser 60 and the closing of the switch contacts initiating
`a new sequence of measurement.
`While I have shown in this apparatus only two or
`three measurements of physical functions of a being it
`should be recognized that other physical properties can
`be sensed and recorded in a similar manner.
`It should
`be recognized, however, that this apparatus provides a
`simple, and accurate means of measuring systolic and
`diastolic blood pressure while at the same time utiliz-
`ing these measurements for determining pulse rate. Fur-
`ther. the measurement is taken on a rise in pressure at
`which point the pressure is released from the portion
`of the body in which blood is occluded to provide for
`a minimum of period of time during which the clamp-
`ing or occluding process takes place. This minimizes
`the physical discomfort and abnormal efiects on the
`portion of the body involVed such that repeated measure-
`ments may be taken with repeatability and accuracy of
`results.
`In considering this invention it should be remembered
`that the present disclosure is intended to be illustrative
`only and I wish to be limited only by the appended
`claims.
`Iclaim:
`1. Apparatus for automatically sensing and recording
`a plurality of body functions comprising a primary sensor
`including a light source and photocell combination and
`a variable pressure clamping means, a source of variable
`pressure connected to said clamping means, means for
`cyclically adjusting said pressure source, signalling means
`connected to said clamping means for converting varia-
`ble pressures therein to an electrical signal output propor-
`tional
`to the same, said sensor being adapted to be,
`mounted on a body and so aligned that when said sensor
`is associated with a body said clamping means can alter
`the flow of blood through a portion of the body affected
`by said clamping means to vary the amount of light
`from said light source to said photocell, said photocell
`when so clamped on a body being adapted to produce
`an output of pulsed signals in accordance with blood
`flow providing a maximum output in accordance with
`a lack of blood in the portion of the body when clamped
`and a minimum output under normal conditions of
`blood flow in the body, a first circuit means connected
`to said photocell and including a voltage peak detecting
`circuit means, an amplifier, a relay connected to and
`controlled by said amplifier connected to said peak
`detecting circuit and providing pulsed operation of said
`relay in accordance with pulsed input signals thereto
`from said photocell as long as each succeeding pulsed
`signal is larger than the preceding signal, switching cir-
`cuit means including a part of said relay of said amplifier
`and cennected to the signalling means, a memory circuit
`means including a Capacitor Connected to said relay
`switching circuit means and adapted to [receive the signal
`output from said signalling means with each pulsed oper-
`ation of said relay means, first Output circuit means con-
`nected 'to said memory circuit means and responsive to
`the signal on said capacitor, second circuit means con-
`nected to said photocell and responsive to the pulsating
`signal output thereof,'a second amplifier and relay means
`connected to said second circuit means and operated in
`accordance with said pulsed signal output,
`second
`switching means included in said second relay means con-
`nected to said signalling means, memory circuit means
`including asecond capacitor connected to said second
`relay switching means and responsive to the output of
`
`8
`said signalling means, second output circuit means con-
`nected to and responsive to the signal on said second
`capacitor, third circuit means connected to said first on-
`cuit means and including a stepping relay respousive to»
`the pulsed output of said photocell, transducer means
`providing an analogue signal output connected to said
`stepping relay means, a recorder, and a motor driven
`switching circuit means cyclically connecting said first
`and second output circuit means and said analogue
`transducer means to said recorder.
`2. Apparatus for automatically sensing and recording
`a plurality of body functions comprising a primary
`sensor including a light source and photocell combina-
`tion and a variable pressure clamping means, a source
`of variable pressure connected to said clamping means,
`means for cyclically adjusting a pressure source, signal-
`ling means connected to said clamping means for convert-
`ing variable pressures therein to an electrical signal out-
`put proportional to the same, said sensor being adapted
`to be mounted on a body and so aligned that when said
`sensor is associated with -a body said clamping means
`can alter the flow of blood through a portion of the
`body affected by said clamping means to vary the amount
`of light from said light source to said photocell, said
`photocell when so clamped on a body being adapted to
`produce an output of pulsed signals in accordance with
`blood flow providing a maximum output in accordance
`with a lack of blood in the portion of the body when
`clamped and a minimum output under normal condi-
`tions of blood flow in the body, a first circuit means
`connected to said photocell and including a voltage
`peak detecting circuit means and an amplifier, a relay
`connected to and controlled by said amplifier connected
`to said peak detecting circuit and providing pulsed op-
`eration of said relay 'in accordance With pulsed input
`signals thereto from said photocell as long as each suc-
`ceeding pulsed signal is larger than the preceding signal,
`switching circuit means including a part of said relay
`of said amplifier and connected to the signalling means,
`a memory circuit means including a capacitor connected
`to said relay switching circuit means and adapted to re-
`ceive the signal output from said signalling means with
`each pulsed operation of said relay means, first output
`circuit means connected to said memory circuit means
`and responsive to the signal on said capacitor, second
`circuit means connected to said photocell and responsive
`to the pulsating signal output thereof, a second amplifier
`and relay means connected to said second of circuit
`means and operated in accordance with said jpulsed signal
`output, second switching means included in said second
`relay means, connected to si