WO1987000027A1 - Oxymetre et systeme d'oxymetrie - Google Patents

Oxymetre et systeme d'oxymetrie Download PDF

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Publication number
WO1987000027A1
WO1987000027A1 PCT/JP1986/000342 JP8600342W WO8700027A1 WO 1987000027 A1 WO1987000027 A1 WO 1987000027A1 JP 8600342 W JP8600342 W JP 8600342W WO 8700027 A1 WO8700027 A1 WO 8700027A1
Authority
WO
WIPO (PCT)
Prior art keywords
oximeter
warning
signal
output
pulse rate
Prior art date
Application number
PCT/JP1986/000342
Other languages
English (en)
Japanese (ja)
Inventor
Kenji Hamaguri
Takao Sakai
Akio Yamanishi
Hitoshi Kamezawa
Original Assignee
Minolta Camera Kabushiki Kaisha
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from JP60148548A external-priority patent/JPS628738A/ja
Priority claimed from JP61062986A external-priority patent/JPH0732767B2/ja
Application filed by Minolta Camera Kabushiki Kaisha filed Critical Minolta Camera Kabushiki Kaisha
Publication of WO1987000027A1 publication Critical patent/WO1987000027A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue

Definitions

  • the present invention relates to an oximeter for non-invasively measuring oxygen saturation in blood and an oximeter system using the same.
  • Print-out function A function to immediately print the measurement results of Sa ⁇ a on the paper.
  • a dedicated or general-purpose recorder is used for the conventional Oximeter, or the measured value is transferred to an external device such as a printer or a computer.
  • a terminal for outputting a digital signal is provided, and the measured value can be output to the external device through a connection cable.
  • Such output terminals simply output the measured values that are continuously measured from time to time, so that the output can be used for trending and printing with an oximeter.
  • An add function and a data analyze function can be added. To this day Taanara Lee's function was allowed to develop ⁇ , and the child is considered to cormorants by Ru can be measured for a long time the S a 0 2 of the patient during daily life. To do so, the oximeter must be configured to be portable.
  • the memory means for recording the measured values and the data stored in the memory means are used.
  • a means to analyze the data after collection is needed. Therefore, if a memory built in a computer, which is an external device, is used as a memory means, the main body of the oximeter and the computer can be connected at the time of data collection.
  • the device to be measured must be carried, and the equipment to be carried is heavy and bulky, which is inconvenient.
  • external noise is Or disconnection of the connection cable is likely to occur, and the reliability of the device is reduced.
  • the integrated dedicated oximeter having the trend function and the data analysis function has a certain power, it is much larger and heavier. There is a deficiency that a wave measurer or 'wave carrier' cannot be used when collecting measurement data.
  • S a ⁇ 2 which is an index of the respiratory condition, is measured for the following two main purposes. The first is to examine R-phase changes in the patient's condition. In this case, it is only carried out several times a day to as measurements of S A_ ⁇ 2 rather high. Measurements made for this purpose This is called spot measurement. S A_ ⁇ 2 Have another an object to measure is to constantly monitor whether there is abnormality in the patient during hand surgery and oxygen therapy. In this case, S a O 2 must be measured continuously over the R time. This measurement is called continuous measurement.
  • Apparatus for measuring the S a O 2 O key sheet menu chromatography data
  • O key sheet menu chromatography data O key sheet menu chromatography data
  • Apparatus for measuring the S a 0 2 above has two purposes Nodea also useful in order to achieve respectively, conventionally, had example, if Sho 6 0 - proposed in 1 7 6 6 2 4 No., etc. ing.
  • conventional devices are either dedicated to spot measurement or dedicated to continuous measurement, and there is no single device capable of performing both of the above purposes.
  • Oximer dedicated to spot measurement only displays the measured values, so the operator must record the measured values in order to perform continuous measurements, and that record Since data analysis has to be performed based on the measured values, continuous measurement is indispensable.
  • an oximeter dedicated to continuous measurement is not suitable for spot measurement because it has a power supply and data analyzer for continuous measurement, so the device itself becomes large in size.
  • the purpose of the present invention is to provide an oximeter that can be provided with a data analysis function and that can be carried by the subject. is there.
  • Another object of the present invention is to make it possible to easily analyze continuously measured data such as Sa02 in the form of '; Data * system is to be launched.
  • Still another object of the present invention is to provide a high-precision non-invasive oximeter having both the function suitable for spot measurement and the function suitable for continuous measurement described above. To do. Still another object of the present invention, various data not measured S a 0 2 only are stored at the time of measurement, Ki ⁇ been de - performs display easily analyzed for diagnostics based on data The aim is to provide an oximeter system that can do this.
  • Another object of the present invention is to separate a data collection device for collecting data from a patient and a data analysis device for analyzing the collected data from each other so that data collection is performed.
  • the data stored in the memory of the device can be used for data analysis and measurement data can be analyzed and displayed by the data analyzer.
  • the present invention relates to an oximeter for measuring the oxygen saturation of a spring to be measured, wherein the light emitting means projects light toward the measured object, and the light emitted from the light emitting means passes through the non-measured object.
  • Light receiving means for receiving light, calculating means for calculating the oxygen flatness and pulse rate according to the output signal of the receiving means, and a warning value for setting a warning value for the oxygen flatness and a warning value for the pulse rate
  • Warning means for outputting a warning signal when connected, time measuring means for measuring time, ⁇ means, light receiving.
  • the time A control means for storing the calculated oxygen plane flatness, the calculated pulse rate, the set oxygen saturation warning value, the set pulse rate ⁇ s-value, and the output of the warning means in the storage means It is characterized by having.
  • the eleventh eleventh is a circuit showing the oximeter body of the first embodiment of the present invention.
  • Road map, Fig. 2 is an external front view
  • Fig. 3 is a circuit diagram showing the state where the oximeter body and the AC adapter are connected
  • Fig. 4 is an external front view showing the state
  • Fig. 5 is a circuit diagram showing a state where the data analyzer and the data analyzer of the main body are connected
  • Fig. 6 is an external front view showing the state
  • Figs. 7 and 8 are data analyzers.
  • FIG. 9 is a circuit diagram showing a state in which the oscillator main body and the printer are connected
  • FIG. 10 is a bottom view of the appearance showing the state.
  • Fig. 11 is a circuit diagram showing the state where the oscillator unit and the transmitting unit are connected.
  • Fig. 12 shows the state where the receiving unit and the data analyzer are connected. Circuit diagram,
  • FIG. 13 to FIG. 16 are block diagrams showing various modes of the oximeter system of the second embodiment of the present invention
  • Fig. 18 is an electric circuit diagram showing the configuration of the rush current control unit
  • Fig. 1 S is a waveform diagram showing the output waveform of each unit
  • Figure 0 is a block diagram showing the configuration of the signal processing unit
  • Figure 21 is a waveform diagram showing the driving waveform of each L LI)
  • Figure 22 is the relationship between the output of the amplifier and the frequency.
  • the graph shows that the output and frequency of the synchronous rectifier are the same as the output of the synchronous rectifier. : Graph showing output change with the parameter, FIG.
  • FIG. 25 is a D-chart showing “LED driving frequency setting routine” of this embodiment
  • FIG. 26 is R high.
  • Pass filter I, ⁇ 27 and 28 are waveform diagrams showing the operation
  • FIG. 23 is a timing chart for explaining the crosstalk.
  • FIG. 30 is a front view showing the configuration of the display unit and the operation unit of the main body of the present embodiment.
  • FIG. 31 is a flowchart showing the operation of the book in the present embodiment.
  • a chart showing the “alarm sound mode setting routine” is shown in Fig. 33.
  • Fig. 34 shows the "AZD conversion routine" with 7 ports-the chart
  • Fig. 34 shows the "LED light quantity so-called regular routine"-Fig. 35 shows the "AZD conversion routine".
  • FIG. 36 is a flow chart showing the “measurement stop routine”
  • FIG. 36 is a flow chart showing the “measurement stop routine”.
  • Fig. 38 shows the flow chart showing the "digital output 1 routine”.
  • Fig. 38 shows the flow chart showing the "digital output 1 routine”. its "data Note Li ⁇ sense Lou Chi down” the shown to full b over Ji ya - DOO, 4 0 Figure full b Chiya one preparative indicating the "S a 0 2 stability determination Lou Ji emissions”
  • Fig. 41 is a flow chart showing the "digital output 2 channels”
  • Fig. 42 is a flow chart showing the "pulse wave sound processing area”.
  • 43 is a block diagram showing the configuration of the printer, Fig.
  • FIG. 44 is a front view of the printer
  • Fig. 45 is a flow diagram showing the operation of the printer.
  • Fig. 46 shows an example of the printer's printout.
  • Fig. 47 to Fig. 4S show the detailed operation of the printer.
  • FIG. 50 is a circuit diagram showing a more detailed configuration of the data analyzer shown in FIG. 5, and FIG. 50 is an operation when the power of the data analyzer is turned on.
  • FIG. 52 shows a ⁇ -chart representing an operation in the analysis mode
  • FIG. 53 shows a storage state of the storage unit.
  • f Explanation diagram Fig. 54 is a flowchart showing the operation of the entire data reception routine
  • Fig. 55 is a flowchart showing the operation of the analysis processing loop.
  • FIGS. 2A and 2B are explanatory diagrams showing an example of a displayed histogram.
  • the oximeter in this embodiment can be provided with a trend function and a print analyzer function in addition to a portable data analysis function.
  • O key sheet menu over data body (A) is connected to the probe having a light projecting element Oyo shed 'receiving 3 ⁇ 4 element - for calculating the S a 0 2 and pulse rate Te Control of the analog section (1), which outputs the analog signal, the analog section (1), the multiplexer (3), and the memory (6 and the parallel renorial conversion section (4)).
  • the display unit (7) that displays the output of the conversion unit (4) and the arithmetic control unit, the analog unit (1), the arithmetic control unit (2), the multiplexer (3), and the serial It consists of a Ralelle conversion section (4), a clock section (5), and a power supply section (8) for supplying power to the memory (G).
  • the power supply (8) has a built-in rechargeable battery and can supply power to the oximeter body (A) without using commercial power.
  • the power supply Yasuko is connected to (1), and it can be operated using commercial power, and the built-in battery is also charged.
  • Ana ⁇ grayed section (1) is, S a0 2, and outputs a signal for calculating the pulse rate and pulse waveform calculation control unit (2).
  • Calculation control unit (2) is S a0 2 and AZD converts the output of the ⁇ analog section (1), calculates the pulse rate and pulse wave at predetermined time intervals.
  • Calculation control unit (2) inputs the output or time of the clock unit (5) for each predetermined time, the S a0 2, to Ki ⁇ the pulse beats and time Note Li (6).
  • the arithmetic and control unit (2) is provided with input terminals (a) and (b) for identifying which dedicated device the oximeter body (A) is connected to.
  • Each part is controlled by the connected dedicated device, and the real-time SaO 2 , pulse rate, time, and time are output from the arithmetic and control unit (2) according to the dedicated device.
  • any of SaO 2 , pulse rate, and time stored in the memory is selected by the multiplexer (3).
  • ⁇ Force of multiplexed Selector Selector support (3) is Ri parallelogram Le signal der, which is converted to The serial signal parallelogram Resid real conversion unit (4), S a0 2, pulse rate, time of de - Is output to the connected dedicated device via one connection signal line. Since the serial signal is output to the dedicated device in this manner, the number of connection signal lines for outputting to the zero-use device can be reduced, and the reliability of the system can be improved.
  • the multiplexer (3) and the parallel-to-serial converter (4) do not operate. This reduces power consumption and extends battery operation time. be able to.
  • the MODE button (1 2) is pressed until "L" SAT "is displayed in the mode display (15), the set SaO 2 lower limit is displayed on the SaO 2 display (3). Is displayed.
  • the upper limit of the pulse rate can be obtained by pressing the M0DE button (12) until "HIP.R.” is displayed on the mode display (15). With the upper limit of the pulse rate displayed on the display (10), press the up button.
  • the alarm sound can be selected by pressing the ALARM button () 7).
  • “(( ⁇ ))” is displayed on the alarm sound display section (16)
  • a warning sound is emitted when the above-mentioned warning state is entered, and the warning sound is not emitted when "(( ⁇ )))" is not displayed.
  • the mode display (15) When neither is displayed, that is, in the measurement mode, the UP button (13) or the D ⁇ WN button Press (14) to adjust.
  • the warning sound is output regardless of the warning sound generation setting, and the user can adjust while checking the volume.
  • the volume is adjusted, it is displayed on the set volume level pulse wave display section (11) so that the volume can be checked visually.
  • the time of the built-in clock is adjusted using the TIME button (18), the UP button (13), and the D0VN'N button (14).
  • TIME button (1 3) is pressed first, "TI ⁇ ⁇ " is displayed on the TI ⁇ display (2 1).
  • the moon flashes on the SaO display (9), and the pulse rate In the display section ( ⁇ is displayed at 1 en.
  • t p button
  • the oximeter (A) is provided with a pulse wave sound generating means synchronized with the pulse so that it can be confirmed whether or not the pulse wave is correctly detected.
  • the generation and stop of the pulse wave sound can be switched by pressing the PULSE button (19).
  • the display of the oximeter (A) uses liquid crystal, and the display cannot be seen in dark places such as at night. At this time, when the I GHT button (20) is pressed, the entire display is illuminated and each display can be checked.
  • the battery (display) 2 2 When not using the AC adapter (B) or the data analyzer (C) with the battery charger (A), ie when operating from the built-in battery, the battery (display) 2 2) "BATT" is displayed. When the built-in voltage drops and needs to be recharged, the warning sound is emitted for a short time, and the "BATT" display flashes to warn the user of a warning. Can be prevented.
  • Fig. 3 shows a block diagram when the oximeter (A) and the AC adapter (B) are integrally connected
  • Fig. 4 shows the appearance when they are connected.
  • the AC adapter (B) is used to operate the oximeter (A) with the quotient power supply and to charge the battery built into the oximeter (A).
  • S ⁇ 0 Pulse rate can be output to a general-purpose recorder and a combi- ter to add a trend function.
  • (23) is a serial converter that converts a serial signal to a parallel signal.
  • BAD La Le Le conversion unit (2 4) (2 5) each S a0 2 pulse rate, re g capacitor for temporarily storing the time, (2 6) each unit braking Gosuru controller of the AC adapter (B) , (2 7) is S A_ ⁇ 2 and pulse rate i te-safe i scan standards RS 2 3 2 di di capacitor Le output unit converts and outputs the output format of the C, (2 8) is S D ZA converter for outputting A_ ⁇ 2 and the pulse rate in analog signal, (2 S) is a power supply unit for supplying power to each unit, rectifying the commercial power source voltage inputted from (3 0) ho pin) The rectifier supplies power to the voltage section (29) and the power section (S) of the oximeter (A) via the terminals (e) and (f). The battery built in the power supply section (8) of the simulator (A) is also charged.
  • Oximeter (A) from control unit (26) to terminal ⁇ )) ( ⁇ : Outputs a signal that identifies that the connected device is an AC adapter (B).
  • ⁇ Outputs a signal that identifies that the connected device is an AC adapter (B).
  • a multiplexer is selected so that the Sa ⁇ pulse rate output from the arithmetic control section (2) is input to the parallel-to-serial conversion section (4), and the parallelizer is selected. Only S: and the pulse rate are output from the serial conversion unit (4) to the ⁇ C adapter;). Time data does not need to be output to the C adapter (B), and time data is not output to reduce power consumption.
  • the Sa02 and pulse rate output from (26) are calculated by the DA converter.
  • BAD picture sound In (28) they are converted to analog signals (for example, voltage) and output to Yasuko (h) and).
  • Fig. 5 shows the block diagram
  • Fig. 6 shows the appearance of the connector.
  • Day Taanara Lee The (C) is O key sheet S a 0 2 Oyo Pi graph the pulse rate in real time Lee Tsu Kdei spray Lee (3 7) for outputting either menu chromatography data (A) and graph I It is displayed and recorded on a pickup printer (49) to add a trend function.
  • a data analyzer function can be added to analyze the measured values of SaO 2 and pulse rate over R time, which was collected by the oximeter (A) alone.
  • the data analyzer (C) receives the serial signal output of the oximeter (A) via the terminal (d) and converts it to a parallel signal.
  • the third register (3) temporarily stores the data of SaO: converted into parallel signals ⁇ by the serial / parallel converter (31). 2), 4th register (33) to temporarily store pulse rate data, 5th register (34) to record time data ⁇ time register, and 3rd register (3) 2), 4th register (33) and '5th register (3'i,' Sa 'written in'', pulse rate, time data are input.
  • the arithmetic and control unit (35), which controls each unit as well as the control of each unit, and the S a O 2 and pulse rate output from the performance control unit (35) are defined as time and A display section (37) that also displays graphs and digital data, S a ⁇ output by the computation control unit (35): a printer unit (33) that records pulse rate data in a graph with time, selection of a graph display method,
  • BAO ORIGINAL Part (3 3), arithmetic and control unit (3 5) S a0 2 outputted from analog output unit for analog output data of pulse rate (4 0), the output of rectifying the voltage of the commercial power supply
  • the rectifier (4) supplies the power to the oscillator (A) via the terminals (e) and (f) and also supplies it to the power supply (41) of the data analyzer (C). 2) A power supply section (41) that stabilizes the output of the rectification section and supplies power to each of the above blocks.
  • the operation modes of the data analyzer (C) include a real-time mode and an analyze mode.
  • Analyze mode is defined as an oximeter (A).
  • the real time mode is the R button (43)
  • the multiplexer (3) is controlled so that it is output to the data analyzer (C). If the SZS button (-45) is not pressed, the parallel-to-serial conversion unit (4) does not perform the operation, so that power consumption can be saved.
  • the serial signal is converted to a parallel signal and temporarily stored in the third register (32), the fourth register (33), and the fifth register (34), respectively.
  • Arithmetic control unit S A_ ⁇ 2 pulse rate input to the (35), the arithmetic and control unit (35) each display unit also time and Yoko ⁇ in Note Once re in the storage and in the graph is displayed, the latest S a0 2, are displayed by the number woo pulse rate Ho display unit.
  • the S a0 2 pulse rate and other measurements Tato example, if blood pressure, respiratory rate, brain waves, an electrocardiogram and also to record the de - to jar by data collection can be performed, Ana log output section (4 0) and S a0 2 and through de-di- data Le output unit (3 3), pulse rate data is output.
  • the horizontal glaze scale of the graph display can be selected according to the record speed button (46) in the control section (36).
  • the paper feed speed is selected using the record speed button (46).
  • Sa0 2 select the vertical axis of the pulse rate using the control ⁇ -button (36) with the first scale button (4 ⁇ ) and the second scale button (4S). .
  • SZS button 45.
  • S / S button i5, 'When the measurement is completed by pressing it, the parameter * of the oximeter (A) will be changed so that the operation of the real conversion unit (4) stops.
  • a signal is sent from the arithmetic control unit (35) of the data analyzer (C) to the arithmetic control unit of the oximeter (A). .
  • trend monitoring of SaO 2 and pulse rate can be performed.
  • press the A button (44) to switch to the analysis mode and it will be stored in the memory of the arithmetic and control unit (35). In this way, you can analyze the measured values.
  • the zoom mode is selected by pressing the A button (44).
  • the arithmetic control unit (2) of the oscillator is informed of the analyze mode via the arithmetic control unit ⁇ terminal ⁇ ) ⁇ ) ⁇ ), and the arithmetic operation is performed.
  • the SaO 2 , pulse rate, and time over the dwell time recorded in the control unit (2) and the memory (6) are parallel and serial signals via the serial conversion unit (4).
  • the multiplexer (3) is controlled so that the data is output to the data analyzer (C).
  • the SaO 2 , pulse rate, and time data stored in the memory (6) are converted to parallel signals by a terminal () through a serial ⁇ parallel conversion unit (31).
  • the 3rd register (32), the 4th register (33), and the 5th register (34) are temporarily stored and input to the KI and calculation control sections (35), respectively.
  • a warning is displayed on the display (37).
  • the contents of the memory (6) are automatically cleared to prepare for the subsequent data collection.
  • one source Rubota down ( 50) or 2nd force — can be moved by operating the button (51), and when enlarging a part of the graph; Move the cursor to the position of the time that is being enlarged by the first cursor button (50) or the second cursor button (51), Pressing the 1 button (52) moves the time at the cursor position to the middle of the display. Next, adjust the scale of the time sleeve with the large button (53) and the reduced button (54). The vertical glaze of SaO 2 and the pulse rate displayed on the display (37) when enlarged is the first scale button (47) and the second scale button (8). Is selected.
  • the maximum in the range displayed graph is the minimum value.
  • Each frequency distribution is also a frequency distribution of data within the range displayed in the graph, and the measurement time within the range displayed in the graph is displayed.
  • Fig. 3 and Fig. 10 show the block diagram and j: appearance at this time, respectively.
  • the printer (D) is mainly used for spot measurements, ie not continuous-used to print the measured values during only one measurement.
  • the printer (D) is connected to the serial signal output of SaO 2 , pulse rate, and time from the parallelizer (4) of the oximeter (A).
  • a parallel serial conversion unit (56) that converts the parallel signal into a parallel signal via the parallel signal, and stores the SaO : pulse rate and time data converted into the parallel signal for each hour 6 Register (57), No.
  • the printer unit (61) to S A_ ⁇ 2 pulse rate, time It consists of a control unit (60) for controlling to print, a printer unit (61) for printing Sa 12 , pulse rate and time. Power to each part of the printer (D) is supplied from the oscillator (A) via the element (k).
  • the Prin data (D), S a0 2 pulse rate is professional - and to Shirushi ⁇ the measured values to the automatic can that Tsu name to the state that can be correctly measured after blanking apparatus AUT 0 mode, flop can the Li te Prin provided et been to (D) preparative port data down (6 2) is pressed, the a Kino S A_ ⁇ 2, MANUAL to Shirushi ⁇ measurements of pulse rate mode - A mode switch (63) for selecting the mode and is provided.
  • AUT 0 can a mode is selected, after the blow over blanking is attached to the subject, S aO-2, pulse rate number of data sequentially inputted to the control unit (6 0) is given Judgment is performed to determine whether or not it is stable within the range. If it is stabilized, it is determined that the measurement can be performed correctly, and the measured value at that time is printed together with the time at the Digitally printed in 1). In the above judgment, the control unit confirms that the A
  • the operation can be performed by the arithmetic control unit (2) of the oscillator (A).
  • the operation of the parallel-to-serial conversion unit (4) is stopped until the measurement can be performed correctly, and when the measurement can be performed correctly,
  • this telemetry unit is composed of a transmission unit (E) and a reception unit (F).
  • the transmitting unit can be connected to the transmitter (A), the AC adapter (B), and the transmitting unit (E). - 'bodies to can also fix the binding to base head, S A_ ⁇ 2 of the patient over ft time using commercial power, the pulse rate motor two motor - that Ki de and child are.
  • Fig. 11 shows the configuration when the transmission unit (E) and the oximeter (A) are combined.
  • the transmission unit (E) is connected to a modulator (64) that modulates the serial signal output of the parallel serial converter (4) of the oximeter (A).
  • the output of the modulator (64) is received by light, radio waves, or ultrasonic waves.
  • the control unit (66) informs that the transmission unit (E) is connected to the control unit.
  • the oximeter ( ⁇ ) is connected to the terminal D through terminals (a), (b) and (c).
  • Unit (66) recognizes that it is connected to the transmission unit (E) and outputs it from the arithmetic control unit (2).
  • the multiplexer (3) is controlled so that the signal is transmitted from (4) to the transmission unit (E) via the terminal (d). 'Parallel serial converter
  • the output of (4) is amplitude-modulated by the modulator (64) and output from the output unit (65) to the receiving unit (F).
  • the modulation in the modulator (64) may be FM modulation or phase modulation.
  • Fig. 1'2 shows the configuration when the receiving unit (F) is integrally connected to the data analyzer (C).
  • Receiving Uni Tsu preparative (F) is transmitted
  • the control unit (A) sends a signal to the data analyzer (C) to identify that the reception unit (F) is connected to the data analyzer (C).
  • S;: Real-time mode must be selected until the data analyzer (C) has completed data approval
  • the line for transmitting the data of SaO 2 , pulse rate, and time is transmitted separately to the line for transmitting the data of SaO 2 , pulse rate, and time.
  • the output of the dedicated oximeter system according to this embodiment is output from one signal line according to each dedicated device, the power consumption is small and the battery can be used for a long time.
  • the main body of the oscillator and the dedicated device are integrally connected without a connection cable, and signals are transmitted and received only through the connector. Therefore, the influence of external noise is small and there is no failure such as a new connection cable, so that the reliability is high.
  • the portable battery can be operated with a small footprint of the oscillometer itself; Sa0 2 measured over the R time, the pulse rate is stored, and the time of the If Since it has a memory that can be stored in memory, it is possible to accurately measure SaO: and pulse rate during daily operation of the patient or the subject, and after data collection, read the By setting the data in the data analyzer, the collected data can be easily broken.
  • the small-sized oscillometer main body you can select a combination that suits the required functions. Therefore, a system with high cost performance can be formed.
  • the nit (E) is mechanically connected to the body by a connecting means (not shown), and for example, by a pin-junk connection! ) It is configured to be electrically connected without using a cable.
  • these devices have a built-in micro computer, which
  • the display means and the real-time plane flatness information output means from the above-mentioned xymeter body (A) are reduced. With this configuration, the portability may be further improved.
  • (103) is a special printer as shown in Fig. 1 '4.
  • the main body (10S) is a general-purpose information processing device such as a personal computer.
  • the IC card (1.02) inserted into the main body (103) is detachable, and the Sa card written on the IC card (102) can be removed.
  • the data such as the pulse rate is analyzed by inputting the I 'two-card (102) into the dedicated processor (10S) shown in Fig. 16. You can do it.
  • FIG. 17 shows the general configuration of the probe (101) and the main body (103).
  • a signal circuit (107) for processing the output of the light-receiving element (125) in the blower (101) described later, and a signal ⁇ A multiplexer (108) for selecting the output of the logic circuit (107), an AZD converter (109) for converting the output of the multiplexer (108) to a digital signal, sa0 2 and computation of pulse rate, and later displaying unit (1 1 3) or the operation unit (1 1 4) or the like rows of cormorants
  • the probe (10 1) emits RL (approximately 660 ⁇ ) and emits ED (1 2 — 1), with RL D D () 20) and 340 near ⁇ .
  • the temperature detector (122) that outputs a signal corresponding to the temperature of the RLED (122) or IRLED (122), and the RLED (122) has a 9 0 0 ⁇ « ⁇ is a harmful level output section (123) that outputs a signal f" corresponding to the nearby light emission intensity, a spot measurement probe or an irregular measurement probe- Output from the probe identification output unit (1, 4), RLED (120), and IRLED (122), which output a signal for discriminating whether or not the probe It consists of a light receiving element (125) that emits light and outputs a signal according to its intensity.
  • the power supply (110) is an N ⁇ Cd battery (126) that supplies power to each part, and the RAM (111) is used when the power switch is off.
  • Power to each section is supplied from the constant voltage output section (134).
  • the power supply uses a NiC bus / terimeter (126), the measurement can be performed even when the main body (103) is moved. Suitable for sport / port measurement.
  • the AC power supply can be connected to the main unit (103) by connecting the AC adapter to the external power input (128). It can also be supplied. Charging of the CJ battery (12) is also performed via an AC adapter connected to the external power input section (12).
  • the C d vano battery (1 26) has a short life when overcharged, and is dangerous because it causes liquid leakage and temperature rise.
  • N d C When the main battery voltage detection unit (131) detects that the voltage of the battery (1226) has reached a predetermined value (first detection level); The charging current is suppressed to the level that is input to the overcharge prevention unit (1 2 3) and stops charging or overcharge does not occur.
  • the AC adapter can be used to connect both the main body (103) and the dedicated printer (104). Can be configured to supply power to In order to operate the main unit (103) and dedicated printer (104) while charging the MiCd battery (126), an AC adapter with a large output capacity is required. In other words, the AC adapter becomes large. Therefore, in this embodiment, when the dedicated printer (104) operates, the dedicated printer (104) operates from the dedicated printer (102). By inputting a charge stop signal (135) to the battery and stopping charging during that time, it is possible to use an AC adapter with ⁇ output capacity.
  • the NiCd battery (126) has a shorter life if overdischarged.
  • the main battery voltage detection unit (131) detects that the voltage of the NiCd battery (126) has dropped below a predetermined level (second detection level). And the detection signal is sent to the CPU (110), and the CP (110) blinks all the segments of the display unit (113) described later, and performs a predetermined operation. A warning sound or the message "L w bat tery" is issued from the audio output unit (115) for a short time to notify the NiCd battery (126) of the voltage drop. Prompt charging.
  • the overdischarge prevention unit (130) operates. As a result, the power supply to the constant voltage output section (134) is stopped, and the overdischarge of the NiCd battery (126) is prevented.
  • NiCd battery (126) is discharged with a large current due to a circuit failure or the like, there is a danger that its life will be shortened and the temperature will rise. You. Therefore, in this embodiment, it is instantaneous that the N; C d battery (126) is discharged with a large current due to a circuit failure or the like.
  • the rated current of (H) is desirable.
  • the power switch (136) is turned off. Then, a large inrush current flows instantaneously to charge the large-capacity capacitor, and the rating of the current fuse ( ⁇ ) cannot be reduced to prevent this. There was a problem. Therefore, in this embodiment, it is possible to use a fuse having a current rating of ⁇ by suppressing the inrush current by the inrush current control unit (133). ing.
  • the suppression of the inrush current can also be realized by a constant voltage circuit having a current limiting function.
  • such a circuit has a large current consumption and a large input / output voltage difference required for normal operation, and is not suitable for a battery-operated device such as the device of the present embodiment.
  • Capacitors: ⁇ :.) (R ⁇ :) are resistors, '' Q—), (Q 4), respectively. Indicates a transistor's transistor and (: C,) IC 2 ) indicates a 3 end-regulator.
  • the inrush current control unit (133) of the present embodiment is
  • Two constant voltage output unit (VC,) (VC 2) have a large ⁇ amount co down Den Sa respectively (C) is Sesshibo, (C.) - Ru and its present ⁇ by the example lever, the power scan I Tsu switch (1 3 6) after on, the time constant of their large co down Den Sa (C JC C :) a and C 4 ', Kemah
  • C JC C large co down Den Sa
  • C 4 ⁇ R The time constant of C ⁇ R and the time constant of C 4 ⁇ R are further differentiated by charging over each listening time.
  • Fig. 13 shows the voltage and current waveforms of each part of the circuit shown in Figs.
  • a backup battery (127) is provided in the power supply (i10 ⁇ ) so that it can be read.
  • a power supply unit (110) a backup battery power detector that detects a voltage drop in the backup battery (12) ! detection unit (132) is provided.
  • the battery voltage of the backup battery is sent to the CP (110).
  • the CPU (110) receives this backup power voltage 2; Warning of low battery voltage.
  • I ⁇ z I ⁇ 2 X ⁇ t ⁇ 2 X ⁇
  • PAD OB NAL S aO 2 Oxygen saturation of arterial blood.
  • the IA tDC I ⁇ 2 DC I ⁇ There I lambda 2 DC certain min respectively, los the (I ⁇ tDC / I ⁇ t ) and log (I ⁇ 2 DC / I ⁇ 2) it each When IHI 2, ⁇ , ⁇ ' ⁇ each is approximately ⁇
  • ⁇ ⁇ 1 81 (E Hb0 2 _ Ii Hb) ⁇ ⁇ + E Hb
  • a light source having a wavelength of about 600 is used as the light source.
  • RLEDs (10) and IRLEDs (11) that emit light having a wavelength near 94 O nm are used.
  • Each LED (10) (11) has an LED driver (11 S) controlled according to the timing created by a timer built in C.pU (l10). ), And each is driven at a duty ratio of 1/2 as shown in FIG.
  • the light emitted from each LED (120) (121) is attenuated through the living organism (155) and received by the light receiving element (125).
  • the light-receiving element (125) outputs a current corresponding to the intensity of the light incident on the light-receiving element, and this output current is converted into a voltage by the current-voltage converter (137).
  • body cormorants I below (1 0 3) sweep rate is to come and is set in the measurement mode one de pitch (S i) is connected to ⁇ (a t), and one 3 ⁇ 4
  • the output of the current-to-voltage converter (137) is amplified by the amplifier (138).
  • the waveform of the output (AJ) of the amplifier (138) is shown in Fig. 21.
  • the output of the amplifier ( ⁇ 3S) is the R synchronous rectifier (133) and the IR synchronous rectifier (140).
  • the R synchronous rectifier (1 3 3) amplifies the input (No.
  • the input signal is amplified by a factor of 1 while (1 2 1) is emitting light, and the input signal is amplified by a factor of 1 during the period when IR LED (1 2 1) is not emitting light.
  • the output of this IR synchronous rectifier (140) is shown in Fig. 21.
  • the output of the R low-pass filter (141) and the output of the IR port-pass filter (142) are, respectively, the intensity of light passing through the living body at around 600 nm and the output of the filter. Corresponds to light intensity near 0 nm. In this way, when the signal due to the light incident on the light receiving element (125) is separated into signals corresponding only to the respective waves R, each LED
  • Figure 22 shows the electrical spectrum of the output of the amplifier (138) when there is a signal due to disturbance light and noise due to the commercial power supply.
  • SP indicates the by that signal component in the light from the LED (1 2 0) (1 2 1)
  • SP 2 is the ambient light component of the low frequency
  • SP 3 and SP 4 is that by the fluorescent lamp or the like disturbances It shows the sum of the high-frequency components of light and the high-frequency components of noise caused by commercial power.
  • fp is the driving frequency of each LED (1 2 0) (1 2 1).
  • the commercial power frequency is 60 Hz
  • the frequency is a multiple of 60 Hz
  • the commercial power frequency is 50 Hz. It is an integral multiple of S 0 H z.
  • the output electric spectrum of the R synchronous rectifier (1S9) is shown in Fig. 23.
  • SP 'indicates a signal component due to light from RLED (120)
  • SP is a component due to SL light of frequency
  • SP 3 ' and SP are fluorescent lamps.
  • Ff shows the sum of the noise caused by the external high-frequency component due to the above and the noise component caused by the high frequency or part of the noise caused by the commercial power supply.
  • the ⁇ - to f ni, _ is over f P: that is a child, etc. correct frequency.
  • the CPU (110) determines the operating frequency of each LED (122) (122) in accordance with the output by determining the commercial power frequency used in (153). Set to a multiple of 0 + 30) H when the commercial power supply frequency is 6 OHz) or a sharp (when the commercial power supply frequency is 50 Hz). I do.
  • the frequency discriminator
  • (153) is composed of a pass filter and a converter having a center frequency of about 55 Hz or 110 H2, and the quotient being used.
  • a square wave of 50 Hz or e 0 Hz is applied to the CP (1 10) depending on 0 HI ⁇ 60 Hz.
  • Fig. 24 Band pass filter and comparator output change of frequency n separate part (153). Output of band 'and pass filter is commercial power frequency. The output of the comparator is a square wave of the same frequency as the output of the bandpass filter. ) Output a waveform in which the waveform of A1 in Fig. 21 is superimposed on the same sine wave as the output of the PAND BUS filter.
  • the LED drive frequency setting routine which is started when (110) is interrupted by the rise or fall of the square wave from the frequency discriminator (15S).
  • the flowchart of the LED driving frequency setting routine is shown in FIG. 25 and will be described. here,
  • the LED drive frequency may be fixed at (common multiple of 60 and 50 + 25) Hz or (common multiple of 60 and 50-25) Hz. In this case, the frequency f separate part (153) is unnecessary.
  • step A when an interrupt occurs due to the rise or fall of the square wave from the frequency discriminator (153), the time T is set in step A to the CPU (110).
  • step B the value stored in the memory address (LT 1) is stored as T 1
  • the value stored at the memory address (LT 1) is read as T 1.
  • the frequency of the commercial power supply is calculated by performing the calculation in step D, and in step D, it is determined whether or not the commercial power supply frequency is 50H.
  • the operation proceeds to step E, and the LED driving frequency is set to 425 Uz Z. If the frequency is not 5 QH. ⁇ , the operation proceeds to step F to increase the LED driving frequency. Set to 5110H2.
  • step G the time T is returned to the address of the memo (L-chome 1): this is stored and the original ⁇ is returned.
  • CP u (l 10) finds the ratio of the output of the co-pass 7 ⁇ filter (1 -'4 1) to the output of the IR ⁇ -pass filter (1 42).
  • the ED drive unit (113) is controlled so that the ratio falls within a predetermined range, and the light intensity of the RLED (120) and the light emission of the IRL DD (: 21) are controlled. Adjust the intensity.
  • CPU (1 10) is the R port — bus filter
  • the gain of the amplifier (138) is adjusted so that the output of (141) and the output power of the IR low-pass filter (142) are within a predetermined range.
  • the output of the Rn-pass filter (142) is connected to a signal line (SI) output to the outside of the main unit (103).
  • SI signal line
  • the multiplexer (144), IR high-pass filter 1 (146), and IR high-pass filter 2 (14C) to input to the '.. Is done. Also, the output of the R high-pass filter I (1447) and the IR high-pass filter 2 (144 are output from the R inverting amplifier (144), respectively. Even if you use the IR-resonator (150), the multiplexer
  • FIG. 26 shows a specific configuration of the R high-pass filter 1 (145) and the R high-pass filter] 1 (147).
  • the IR high-pass filters I (14G) and IR high-pass filters 1 (148) are also R high-pass filters 1 (145) and R high-pass filters, respectively. It has the same configuration as pass filter ⁇ (147).
  • R high- pass off I filter] I (1 4 7) are likewise co Nden Sa (C s), resistor (RJ, It consists of an amplifier (A 2 ) and a switch / switch (S 4 ) whose opening and closing are controlled by a CP switch (110).
  • the amplification ⁇ (A.:: ⁇ _) saturation state at the start of measurement is immediately released by the switch ': S).
  • the R co-gump (1 ⁇ ; 3) output This is the noise that fluctuates at a frequency higher than the frequency of the signal, as shown in Fig. 2C (A). Is included, and the Konoise fluctuates at the R mouth level (1 4 3). Sword output level ⁇ . Therefore, in this laughing facility, the input signal of the S hi-ha filter was 4).
  • BAD ORIGINAL (C) a signal sweep rate I by the pitch from the CPU to the power sale good illustrated (1 1 0) (S 4 ) by instantly on, the low frequency formed Remind as the second 8 view (B) Minutes are reduced.
  • the second 8 diagram (C) is the signal of one cycle day-out sweep rate Tsu Chi (S 4) instantaneously 2 Caio down, once-out 1 cycle Nitsu sweep rate pitch (S 4) It may be configured to turn on.
  • the second 8 views (A) is shown the output-shaped] S that in the prior arrangement does not have a scan I pitch (S 4), and the time and the output level of the whole even It is rising.
  • SR and SMR are output for each predetermined sampling time: the output of the R high-pass 7 filter (1 4 7) that is ZD-converted.
  • the output can be obtained by integrating the output of the R inverting amplifier (144) with the CP (110).
  • the output of the R hyperfilter E (147) and the output of the R inverting amplifier (144) are A / ⁇ D- converted, respectively. It can be obtained from the number of times.
  • the level of arterial blood planarity (SaO :) is calculated by the signal from the RLED (120) and the IRLED (120) in the R synchronous rectifier (139) and IR rectifier (140). 1 2 1) There is no difference between the signal by light from
  • the output of the R synchronous rectifier (13 S) is set to (No. 5 or-G G) by the t from IRLED (1 2 1). Mixed.
  • (1 9 2) and (1 9 3) are RLED (1 2 0),
  • the power switch (136) is first turned on and the switch is turned on.
  • the output of the IR inverting amplifier (150) is subjected to first-order AZD conversion and stored as an offset voltage for each (ST3 to ST8). These are VOLR, VOLIR, VOHR, VORI, VOHIR, and V0IRI, respectively.
  • a signal having the same timing as the RLED drive signal is output to the calibration signal section (151) under the control of CPU (110) (STS).
  • the response speed of the calibration signal unit 1 (151) is adjusted in advance so as to be equal to the response speed including the light receiving element (125) and the current-voltage converter (13). Have been.
  • V CLI IRI corresponds to the GST (S ⁇ 10, S ⁇ 11).
  • a signal having the same amplitude as the output having the same timing as the ⁇ LID drive signal is output.
  • the A / D conversion values of the R-mouth filter (14 1) ⁇ R ⁇ -pass filter (14 2) are assumed to be V CLR2 and V CLIR2, respectively. Write down. ⁇ corresponds to the stock t (S Ti S, ST 14).
  • the ⁇ correct ft number part 2 (15 2) has a predetermined period.
  • the rectangular wave is output to the R high-pass filter 1 (45) and the IR high-pass filter 1 (46). R high pass filter at this time]!
  • the time when the output of the R high-pass filter ⁇ (147) and the output of the IR high-pass filter 1 (144) is positive is denoted by ⁇ .
  • ⁇ the time when the output of the R high-pass filter ⁇ (147) and the output of the IR high-pass filter 1 (144) is positive is denoted by ⁇ .
  • ⁇ the integration of the values obtained by subtracting ⁇ '0HR and " ⁇ ' OH ⁇ R (i) from VHR (;: 'and VHIR (i), respectively, during that time (the values are directly converted to SV PR , SVPIR.
  • the outputs of the R high-pass filter (144 G) and the R high-pass filter (144 G) become negative.
  • T the integrated value of the values obtained by subtracting VORI and VOIRI from VRI ( ⁇ ) and VIRI (i) at that time is one SVMR and one SMPIR, respectively.
  • the values obtained by canceling the low-frequency noise component with respect to SVPR, SVMR, SVPIR, and SVMIR are SVP, SVIR, respectively.
  • the calibration signal 1 is used as the signal for measuring the cost.
  • K 4 measures the temperature of beauty IRLEDs (1 2 1) peak for each LED - I'm on the child correction Flip the shift of the peak wavelength, the measurement result Can be obtained with high accuracy.
  • the temperature of the RLED (122) is measured by the temperature measuring section (122), and the output is converted to AZD via the multiplexer (108) at predetermined time intervals. By doing so, the value of KKKK is corrected.
  • IRLED (1 2 1) to the teeth such as this for measuring the temperature of the measures the temperature of only RLED (1 2 0) is, 9 4 0 n, - fl vicinity of the light - emitting IRLED (1 2 1) System oice of peak wave counter that by the temperature changes in the 'is good to such effect etc. ton ho on measurements of S a 0 2.
  • the temperature of the RLED (120) is measured by measuring the forward voltage of the RLED (120). According to this method, there is no need to provide a special sensor for temperature measurement, so that there is an advantage that the probe (101) can be reduced in size.
  • MotoEmi the ⁇ measures the LED power temperature kappa,, K 2, the kappa 3, K 4 has been shown the method for correcting, R L. ED vicinity 3 ⁇ 4 heat body (1 55 0) Provision, RLED
  • the peak of RLEE> (120) may be kept constant.
  • LEDs that emit near 6 generally have G 60 nrn near the local%) t maxima; this has a submaximal around 900. Therefore, it is necessary to correct KK,, KK 3, and K 4 according to the emission intensity of the RLED (120) around 660 and the emission around 300). Therefore, in this laughing example, ⁇ BAD near S 0 0 of RLED (1 '2 0) The luminous intensity around 660 nta of the light intensity is measured in advance, and the corresponding value is output to the harmful light level output section of the probe (101).
  • Fig. 30 shows the display unit (113) and the operation unit of the main unit (103).
  • (111) consists of a liquid crystal display, and (157) is calculated.
  • S A_ ⁇ second display unit for displaying the S A_ ⁇ 2 measurements
  • a (1 5 8) is pulse rate display unit for displaying the computed pulse rate measurements.
  • (159) is a pulse wave level meter, which lights according to the magnitude of the pulse wave.
  • (1 6 0) is S a 0 2 changing tendency display unit showing the temporal change in S a 0 2.
  • (16 1) is an alarm speaker mark
  • (16 2) is an alarm box mark, each of which displays the mode of the alarm sound. I am.
  • the alarm speaker mark (161) lights up and the alarm sound is turned on.
  • the alarm voice mark is set.
  • (166) is a measurement mode display mark for indicating that it is in the measurement mode, and (166) is a test for indicating that it is in the test mode. ⁇ — Display mark. (1 et 5) S a 0 is displayed when below the lower limit value is set S A_ ⁇ 2 measurements "lower warning Ma - Kudea Ri, (1 6 6) S aO-is that set : Display the lower limit of
  • the pulse rate lower limit warning mark that is displayed when the value falls below the set lower limit value (1 6 8) indicates the lower limit value of the set pulse rate.
  • Section, (16S) is a pulse rate upper limit warning mark displayed when the pulse rate measured value exceeds the set upper limit value, and (170) is the upper limit value of the set pulse rate. This is the pulse rate upper limit warning value display section to be displayed.
  • (1771) A watch clock colony.
  • the power switch of the main body (103) can be used.
  • Test mode Test mode
  • Test mode Test mode
  • Test mode Test mode
  • Test mode Test mode
  • Test mode Test mode
  • Test mode Test mode
  • Test mode Test mode
  • Test mode Test mode
  • Test mode Test mode
  • the test mode is defined by using the calibration signal section 1 (15 1) and the ⁇ ⁇ signal section 2 (15 2) inside the main unit.
  • This mode is used to confirm that the electric circuit in this unit (103) is normal. If it is confirmed that the circuit is normal, the SaO display section (157) and the pulse rate display Part (15S); two "100" are displayed, and when an abnormality II is seen, "E” and the number BAD ORIGINAL Is shown. After confirming that the power circuit is normal in the test mode, press the mode switch (172) again to enter the measurement mode.
  • the memory clear switch (173) is pressed when the power switch (136) is closed, the data storage IC card (102) is pressed. ), The erase command is transferred, and the contents of the IC card (102) are erased.
  • the case of the measurement data! 3 ⁇ 4 will be described later.
  • the clock (11S) When the power switch (13.6) is opened, the clock (11S) is not properly backed up by the built-in backup battery (127). For a predetermined period of time after the switch (136) is closed again, the clock common mark (171) does not blink or stays on. This is a function that allows the user to reset the clock section (11S). -Next, Sa ⁇ : Low limit warning, pulse rate upper limit warning value, and pulse rate lower limit warning Sword setting method].
  • the pulse rate lower limit warning value is set according to (174).
  • the mode switch (1 ⁇ 2) When the mode switch (1 ⁇ 2) is pressed, the mode switches to the pulse rate upper limit warning value setting mode, and the pulse rate upper limit warning mark (169) and the pulse rate upper limit warning are displayed.
  • the value display section (170) flashes, and the pulse rate upper limit is set in the same way by the up-down switch (174).
  • pressing the mode switch (17 2) terminates the above warning value setting mode. Incidentally, even during the set mode of the above warning value, the measurement and display of the S A_ ⁇ 2 and pulse rate is performed.
  • the up-down switch (174) if the up-down switch (174) is not operated for a predetermined time or more in each warning value setting mode, the setting of the warning value ends.
  • the warning value set in this way is always stored in the RAM (112) backed up by the backup battery (127), so that the same warning value is always stored. When the value is used, it is not necessary to set the warning value every time the power switch (136
  • the alarm sound mode The mode switches between voice and warning sound, and the selected alarm sound mode and the set alarm Information on the volume is stored in the RAM (112) backed up by the backup battery (127). Therefore, even if the power switch (13, 6) is released once, the alarm sound mode selected previously and the set alarm volume are recorded on the main unit (103). .
  • the selection of the alarm sound mode is performed by the “alarm sound mode setting step” shown in step # 3 of FIG.
  • FIG. 32 shows a detailed flowchart of the “alarm sound mode setting step”. These descriptions will be described later.
  • pressing the mode switch (172) while holding down the pulse switch (178) causes the pulse wave sound (to be synchronized with the pulse). Sound) can be turned on / off. Also, the volume of the pulse wave sound is the same as the adjustment of the alarm sound volume.
  • the display of "month” in (157) flashes.
  • the setting of the "month” is likewise done by the up-down switch (174).
  • the time switch (173) is pressed, the "day” of the pulse rate display (153) flashes, and the up-down switch (174) is used.
  • the “day” is set.
  • "Sa”: “Hour” is displayed on the display (157) and “Minute” is displayed on the pulse rate display (158).
  • the “hour” indication on the S a O 2 display (157) lights.
  • the “hour” setting is also made by the up down switch (174).
  • the time setting is completed and the mode returns to the measurement mode. If the up-down switch (174) is not operated for a predetermined time or more after the time switch (173) is turned on, the setting of the clock (113) is completed, Return to measurement mode.
  • the alarm mute switch (180) is used to temporarily stop the alarm sound or reduce the volume of the alarm sound after the alarm sound is generated. It is a switch to perform.
  • the state in which the alarm sound is temporarily stopped or its volume is made extremely low is called the alarm mute state.
  • the alarm mute state is released by (1) S a ⁇ 2 or when the pulse rate is released from the warning state.
  • the alarm mute switch (1 S0) or ' If it is pressed again, (2) if it has been more than a predetermined time since the alarm mute state, (2) an alarm sound is generated due to the first cause, and the alarm mute is generated.
  • FIG. 31 shows a flowchart of the operation of the main unit (10S).
  • the power switch (136) is turned on at step # 1 (hereinafter referred to as "stepping the step")
  • step # 2 the power is turned on in the main body (103).
  • Nissharai's ni is performed. 2
  • the memory is measured and the memory clear switch is turned on when the power switch (13S) is turned on.
  • the (1 1 3) clock indicator (1 7 1) lights up and the clock section
  • the user is prompted to set the time of (1 1 3).
  • the measurement mode is executed and the switch is pressed. If it is, the test mode is set and the test mode processing is performed in # 4. After the test mode processing is completed, if the mode switch (17 2) is pressed with 5, the measurement mode is set.
  • the spot measurement mode is executed, or It is determined whether to execute the continuous measurement mode.
  • the continuous measurement mode # 7 or lower is run.
  • RLED (120) and IRLED (122) are driven to start emitting light.
  • the alarm level setting step for setting the Sa0 alarm value, pulse rate upper limit alarm value, and lower limit alarm value is executed as in '; ⁇ . Is done.
  • the alarm sound mode setting step of the 3 2! 21 indication is executed.
  • the alarm sound mode setting stage shown in Fig. 30 is used to set the alarm sound as an alarm sound when an alarm condition occurs. Use a warning sword to warn you, or make a setting to not generate alarm sounds.
  • S1 in the 3rd ; the mode switch (172), the alarm switch (177), and the force f ⁇ 'And S 2 only if pressed simultaneously Proceed to If both switches (1 ⁇ 2 ⁇ (1777) are not pressed at the same time, return to the original flow.
  • the RAM (1 1 2) The alarm sound mode set and stored in is read out, and in S3, it is determined whether or not the current alarm sound mode is the alarm sound 7 mode.
  • AZD conversion of the outputs of (144), IR high-pass filter I [(148), R inverting amplifier (149) and IR inverting amplifier (150) is performed successively. It is. Then, these A / D converted values are integrated by a predetermined number n of samples to calculate the SVR and SVIR. The detailed operation of this AZD conversion routine is shown in the ⁇ -chart of FIG. 33.
  • Fig. 32 first, in (1), the output of the temperature detector (2 2) is AZD-converted and recorded as VTH, and then in (2), the output of the R low-pass filter (144) is output.
  • a / D convert the output and write as ⁇ 'LR), and then in 3 IR port — The output of the pass filter (144) is converted to AZD
  • V LR (originating Bruno of ⁇ Hi 'VLIR ( ⁇ ) both LED using (1 2 0) (1 2 1); LED light amount adjustment Le adjusting the amount - enter the switch down.
  • FIG. S4 This i. RD light intensity adjustment step is shown in FIG. S4.
  • Fig. 4 first, 3-1
  • ⁇ is an IR inverting amplifier.
  • the output of (150) is A / D converted and stored as VIPJ).
  • ⁇ discriminates whether or not the ⁇ / D converted data has reached a predetermined number of samples, and performs steps from 2 to ⁇ until the predetermined number of samples is reached. Return. When it is determined that the number of samples has reached the predetermined value in ' ⁇ ; when it has been reached, the error due to the fluctuation of the baseline is corrected in ® (noise canceling of the ⁇ frequency component described above), and in ⁇ .
  • the crosstalk is measured by the crosstalk measuring pin shown in Fig. 23 and 3 1 Return to the routine shown in the figure.
  • # 13 in Fig. 31 it is determined whether the number of AZD-converted samples has reached a predetermined number n, and the operations from # 8 to # 12 are performed until the number reaches the predetermined clause n. repeat.
  • a calibration constant correction step is next executed at # 14.
  • the output of the temperature detector (122) is subjected to AZD conversion, and the detected constants and the output of the harmful light level output unit (123) are used to calculate the calibration constants, and K in equation (29). 2, the correction of K 3 and K 4 are carried out.
  • pulse wave sound punished 3 ⁇ 4 Le - sets the frequency of the pulse wave sounds generated by Chin ⁇ Ji value to S a0 2 calc.
  • the S A_ ⁇ 2 based on the # 1 in 5 (29) is calculated, the pulse rate in the # 1 6 is calculated.
  • the calculation of the pulse rate is performed as follows. First, the pulse waveform is binarized by the pulse waveform shaping circuit (154), and the rising or falling time is temporarily stored in the RAM (112). Next, the period of the pulse waveform is obtained from the recorded time, and the pulse rate is obtained from its reciprocal. Further, the calculated SaO 2 and pulse rate are displayed on the SaO display section (157) and the pulse rate S display section (15S), respectively. In the event that the Sue is changing at the second time, the upward or downward arrow of the Sa ⁇ : change tendency display (160) is turned on according to the direction of the change. It is.
  • 1 is used to determine a warning condition.
  • S aO and the pulse rate calculated from the AZD conversion result of the signal processing S unit (10 “7”) are correct (measured, so that it is determined whether there is any. N).
  • a predetermined value that is, V LR (i) or V LIR (i) is a predetermined value. If it is larger or smaller, it is determined that the ⁇ -bub (101) is out of the measured area, or that the measured area is too thick to be measured. If the change in the pulse waveform is larger than a predetermined value, it is determined that the measured site has moved.
  • the SaO 2 display section (157) displays the causative force f “C”, “L”, “A” , "P” and so on.
  • each ED (120) (122) is turned on at a predetermined time interval to determine whether or not the measurement capability has returned to the state where normal measurement can be performed. This process is performed in the measurement pause routine shown in FIG.
  • the display proceeds to if 101 and the LED (1 20) (1 2 1) Stop driving, and set CP mode (1 10) to low power consumption mode with ⁇ 102. If the measurement disabled state does not continue for more than the specified time in # 100, return to ⁇ 1G in Fig. 31. From 102, proceed to # 103 to determine whether the measurement mode has been changed. If the measurement mode has been changed, proceed to # 6 in Fig. 31 and change it. If not, proceed to # 104 and wait for the specified time to elapse after the # 102 LED stops operating.
  • SaO lower limit warning, pulse rate lower limit warning, and pulse rate upper limit warning are determined.
  • the calculated SaO and the set SaO lower warning value are compared with it. If the calculated value is less than or equal to the lower warning value, Sa ⁇ : lower warning alarm mark ( 16 5) and the S a ⁇ display (1 5 7) are turned off.
  • the calculated pulse rate and the set pulse rate lower limit warning are compared with the set pulse rate upper limit alert value: The pulse rate is calculated to be less than or equal to the lower limit warning value or the upper limit alert value. If it is higher than S- ⁇ , then the pulse rate lower limit warning mark (167) or the pulse rate upper limit warning mark; 1G3) and pulse rate ⁇ _
  • the display (158) flashes. Furthermore, S aO-2 If the calculated value is less than S A_ ⁇ 2 lower Medogi tell value, there Iho if pulse rate calculated value is out of range of the pulse rate lower warning value and the limit warning value ( ⁇ La chromatography Alarm state), or when it is determined in the warning determination step that the measurement is not possible, a warning sound or voice is issued according to the set alarm mode.
  • a synthesized voice called "Pulse is low" and an intermittent sound having the third frequency are generated. Also, if the upper limit of the pulse rate is warned, in the mode in which the alarm sound is a ⁇ sound only, an intermittent ⁇ with the fourth frequency is generated-and the alarm sound is sounded. In the voice and warning sword mode, a synthesized speech such as "Pulse is.” And an intermittent tone having the fourth frequency are generated.
  • the frequency and the interval between the intermittent sounds are fixed in the above description, but this can be made variable.
  • the degree of danger or the tendency of the danger to become worse or recovering is indicated by sound.
  • an intermittent warning sound of a different frequency may be emitted depending on the cause of the measurement failure. That is, when “C” is displayed as the cause of measurement failure, the intermittent tone at the fifth frequency is displayed, when “L” is displayed, the intermittent tone at the sixth frequency is displayed, and “A” is displayed.
  • the display may be configured such that an intermittent sound of the seventh frequency is generated when it is displayed, and an intermittent sound of the eighth frequency is generated when "P" is displayed.
  • a warning may be issued by voice with respect to the cause.
  • different alarm sounds may be emitted in different continuation states.
  • the following alarm mute processing is performed. If the alarm mute switch (1330) is pressed when the alarm status is 1 or indeterminate status, Stop sound production or set their volume very low and set them to alarm mute state. In the alarm mute state, the alarm speaker mark or the alarm voice mark is displayed according to the specified alarm and mode. Flashes. The alarm or non-measurement state is being selected; when the alarm mute state is set, the alarm mute switch (1 3 If 0; is pressed, the alarm sound or voice is displayed with the volume set in the alarm sound mode setting step, and the alarm sound is output. The alarm status or measurement ready status continues, and the alarm alarm status has already been set and another alarm status or measurement disabled status is set.
  • Alarm sound mode a beep or sound is emitted at the volume set in the alarm mode setting step.
  • the alarm mute state is released when the alarm goes off.
  • the frequency of the alarm sound changes according to the amount of deviation between the set warning value and the measured value (calculated value), and when a predetermined time has elapsed from the occurrence of a warning state or the generation of an unmeasurable state.
  • Fig. 37 shows the flowchart of the Fue embodiment when the volume of the alarm sound is increased.
  • S aO-2 under 'limit warning value one S aO-2 measurements is SaO: lower warning value and S aO-: and Wa table warts or Ru frequency difference between the measured value, y (pulse rate Upper limit warning value-pulse rate measurement value), z (pulse rate lower limit warning value-pulse rate measurement value) Frequency that is higher than the upper and lower limit values of pulse rate and pulse rate measurement by difference from pulse rate measurement It is.
  • the present embodiment Dehoa la - frequency during beam generation, cadence Nitsu, although the priority of the hands is the pulse rate lower limit warning Ru in summer and the first place, S aO-2 lower limit warning or pulse rate limit warnings
  • (AIF 1) has a flag that indicates whether it is in a false state or not.
  • (A ⁇ F) is a flag that is set to "1" in the alarm mute state.
  • (AIF 2) A La chromatography neglected-menu preparative process le over the subsidence - is activated ⁇ / lag (AIF lambda -: Ri COPYING Dea of ', (A ⁇ F 3) New ⁇ A flag indicating that another alarm condition has been determined or canceled.
  • Fig. 37 first, at 2'00, the content of the flag (AIF1) is copied to the flag (AIF2), and is used to determine whether or not the measurement is in the active state.
  • AD dRiC?.! NAL Determine whether or not. If the measurement is not possible, the interrupt for pulse sound generation is prohibited at # 202, and it is determined at # 203 whether the alarm sound mode is off. In here, if in the case of a la over Muonmo over Dogao off the full opening Ichihe Li Turn-down and also, on the other hand alerts Muonmo not an Doka f O 7, # 2 0 The first to indicate the unmeasurable state at 4
  • the audio output unit is set to emit a warning sound with frequency f
  • 2C3 determines whether the AND signal between the flag (AIF1) and "01H” is "01 ⁇ - ⁇ " or not. That is, in the first step, it is determined whether or not the least significant bit (LS #) is “". Here, it does not matter whether or not the bit of # 1 is "”. And this is "0 1
  • # 2 i1 determines whether the alarm ⁇ mode is o7 or not.
  • the second frequency is incremented, and # 213 is used to determine whether the alarm sound mode is the alarm sound only mode. And the alarm
  • BAD ORiGlNAL If the mode is an alarm only mode, set the audio output unit to emit an alarm at frequency f 2 and period T 2 at # 2 14. Hand, # 2 1 3 If it is determined not to be the mode of elbow Tsugeoto only, # 2 1 5 "S a0 2 is low" alternately voice and beep sound period T 2 in the frequency will leave Set the audio output section so that it is emitted to the user. Then, from # 2 14 or # 2 15, go to # 2 16 and set "0 1 ⁇ " to lug 7 (AIF 1). That is, when a Flag (AIF 1) is "0 1 H” (least significant bit is "1”), and this the S aO-2 measurements is below the S aO-2 lower warning value Is shown.
  • the blinking of (1 5 7) is released and # 2 13 determines whether the measured pulse rate is above the pulse rate upper limit.
  • the display section is set so that the pulse rate display section (153) blinks at # 220.
  • # 22 it is determined whether or not the alarm sound is one, and if the alarm sound mode is off, the cuff D is returned.
  • Alarm sound mode must be smart
  • 2 2 7 Rub it and determine if the measured pulse rate does not fall below the lower pulse rate warning value. If the measured pulse rate is lower than the lower pulse rate warning value, set the display so that the pulse rate display blinks in # 228, and press # 22S. Determines whether it is an alarm sound mode or a smart phone. Then, in case of the alarm sound mode, it returns to the original flow, and the alarm sound mode is turned off with # 2 29 '. If not, use # 2 3 0
  • the second frequency is exposed. Further, in # 231, it is determined whether or not the alarm sound mode is a mode for generating a warning ⁇ . If the mode is the mode, proceed to step 232 to determine the frequency and period. ;
  • Warning ⁇ -Alarm sound mode is alarmed by 2 3 1
  • the alarm sound is started. # 2 4 2 to # 2 0 5, # 2 2 6, # 2 3 4 Then, in # 243, it is checked whether the flag (AMF) is "1" or not. The 7 lags (AMF) are set to "1" in the alarm mute state, so the flag (AMF) is set to "1" in # 243. If it is determined, it is in the alarm mute state. In this case, it is determined that the alarm mute switch (180 is pressed or not) is passed to the filter 2 and then the alarm is switched to 2-4. 'Status; distinguish whether the specified time has passed since resetting, and distinguish it from the alarm mute status in # 2445.
  • the place where it is separated is ⁇ 2 4 6 in the flag 7 ⁇ ( ⁇ IF 3), the flag ( ⁇ IF 2) and the flag (AIF 1), and the exclusive exclusive signal of each bit.
  • the signal of the lag (AIF 1) does not change at 7 low from 200 to # 24, the new alarm state is established. If it has not occurred, the flag will be '0H', and the flag will be '0H' from # 200 to 2t2; the flag (AI ⁇ 1) If the signal changes, that is, a new alarm state occurs.
  • ho, Flag (A I F 3) is shall not a "0 0 H".
  • the volume of the two sounds is set to the value set by the volume setting routine, and the flag is set at Hayashi 251, ⁇ MF) is set to "0"; As a result, the alarm mute state is released.
  • the alarm is muted. Since it is not 1, the alarm 2 52 It is determined whether the auto switch has been pressed. Then, the flag ': A / F is pressed;
  • step S254 it is determined whether or not the alarm word-mode is a mode in which only an alarm sound is generated. If it is determined that the mode generates only a warning sound, the alarm is set at # 25 5
  • BAD ORIGINAL Set the peak mark so that it flashes.
  • the alarm voice mark is set to blink in # 256 and # 25 is set. Set the volume of the alarm sound to the minimum in 7 and return to the original flow.
  • the # 7 flag (AIF2) will no longer be "00H” in # 25S. It is determined whether or not a predetermined time has elapsed since then, and if the predetermined time has elapsed, the alarm sound volume is set to the maximum in step 25 3 and the flow is returned to the original flow. On. If the predetermined time has not elapsed since the flag (AIF 2) is no longer “0H” in # 2553, the flow as it is without passing through # 253 Return to.
  • FIG. 31 # 20 The detailed operation of this FIG. 31 # 20 is shown in the flowchart of FIG. 3 ⁇ . ⁇
  • (ALF) is a flag that has the contents shown in Table 1 below according to the set alarm status and measurement capability status
  • (DN) This flag is used to indicate the type of data to be input, as shown in the upper bit No. 2 above.
  • Pulse rate f 3 ⁇ 4 warning value 1 1
  • the data of "Year”, “Month”, “Day”, “Hour”, and “Minute” of the clock section (118) are input / output sections of the CPU (110). It is output from (1 16).
  • the flag (DN) is set to “2” by # 301, and the memory that specifies the contents of the flag (ADR1) indicating the initial address of the memory is set by S302. Set the flag indicating the address (AD1). Then, it is determined whether or not the measurement is impossible in # 303, and if it is in the measurement-ready state, first in # 304, the cause is called a probe (101). It is determined whether or not it is "C" due to the disconnection of the connector connecting the main unit (103).
  • the flag (ALF; is set to "10H") as shown in # 305.
  • 7 lags ( ⁇ LF) are set to" 10 0 ". This is indicated by the binary number of S bit in Table L.
  • the cause of measurement failure is not “C” due to disconnection of the connector, proceed to 30 ⁇ i or S 06, and if the degree is the cause, ' ⁇ It is fixed whether or not it is “L” due to the lower leg, and if the cause is “L” due to the lower leg, the flag (# 307) is used.
  • ALF) is set to "20H".
  • Table 20 shows that the flag (ALF) is set to "20H” in binary G-bit numbers. '
  • # 31S it is determined whether or not the pulse rate upper limit warning has been changed. Then, if the pulse rate upper limit warning value has been changed, the pulse rate power upper limit warning that has been changed in step # 3 17 is stored in a predetermined location of the flag (AD1). # 3 13 Adds "1" to 7 lags (AD 1) and stores them in 7 lags (AD 1), and # 3 1 S adds "3 3" to flags (DN) And store it in a new flag (DN).
  • the operation of # 3 13 is performed by setting “1” to the 6th bit from the least significant bit in Table 2 and setting the pulse to “1”. This is to indicate that this is the data of the upper limit warning value, and to add "1" to the lower bit of the flag (DN) to indicate that the data has increased by one. ,
  • # 320 it is determined whether or not the pulse width lowering warning value has been changed. If the lower limit warning value of the pulse rate has been changed, the changed lower limit warning value of the pulse rate is written in the predetermined address of the flag (AD1) in # 321, and # 3221. Add “1” to the flag (AD 1) to add a new flag (AD 1), and add # 6 23 to the flag (DN) at # 32 3 to add a new 7 lag (DN) Store in
  • the # operation of # 32 23 is that, in Table 2, by setting "1" to the 7th bit from the least significant bit, it is the data of the lower limit of the number of beats. This is done to indicate that data has increased by one by adding "1" to the lower bit of the flag (DN).
  • # 32 it is determined whether or not the event marker switch, which is pressed when an event mark (191) as shown in Fig. 46 is to be printed, is pressed. Judged. If the event marker switch is pressed, add “08H” to the 7th lag (ALF) at # 3225 and store it in the new flag (ALF). This is to set the fourth bit from the least significant bit to "1".
  • the contents of the flag (DN) are written at the address indicated by the flag (ADR1), and in # 3227, the contents of the flag (ALF) are written in the flag (ADR + 1).
  • the flag (0 1 1) to "0 1" 1 in # 3 28.
  • the flags (AD R + 1) and (DN 1) are set. Is the memory It indicates the address and the type of data.
  • the operation of # 328 is performed by taking the AND signal of each bit of the flag (DN) and "0FH". 4 Set the reset signal to the flag (DN1). As a result, only the signal related to the number of data in the flag (DN 1) is left.
  • the flag (ADR1) that is, the initial address is set in the flag (AD1) in # 32, and the contents of the address indicated by the flag (AD1) are output in # 3330.
  • the operations of # 330 to # 3333 are for outputting the contents described in # 320 to # 327.
  • the flag (8 0 1) is added with “1” in # 331, and the flag (0) is added.
  • the flag (DN 1) is stored. This operation is to advance the next address from the flag (ADR1) and repeat the operation of outputting the data written at each address by the number of data while specifying the address.
  • step # 3337 If it is determined in # 3337 that the pulse rate is not higher than the pulsating rate, it is determined that it is not greater than the reported value.In step # 33, the pulse rate is less than the pulse rate warning. Is determined. Then, when it is determined that the value of the number of ⁇ ⁇ is less than the lower ⁇ beat, the value of the flag (ALF) is added to “0 4 H” and a new flag is added. (AL F).
  • the meaning of adding "04H" to the contents of the flag (ALF) is to correspond to the third row in Table 1.
  • each warning value is changed and when the power switch (136) is turned on, each set value of serial communication is changed to a serial interface.
  • Input / output unit externally through the hood It is output as a digital signal from (1 16).
  • RAM card also applies to off n. Y Beady disk or the like. It is also possible to incorporate EEPROM, bubble memory, and memory-backed-up RAM in the main unit to provide the same function.
  • the IC card (102) is sequentially written.
  • the oldest data is erased from the oldest data and new data is written.
  • the IC card (102) stores the latest data for the time determined by the memory capacity. Also, write data when the drowning impossible state is prolonged for a long time. Suspends the process. As a result, the memory in the IC card (102) can be saved.
  • the main body (103) is provided with an event marker switch (not shown).
  • the A signal indicating that the event marker switch has been pressed is output as a digital signal from the output section (116), and the ic card (102) is notified to that effect.
  • the data is transferred and can be used later for data analysis.
  • the time data need not necessarily be recorded for each set of translation data. In the present embodiment, the time is recorded on the IC card (102) when the transmission switch (136) of the main body (103) is turned on and every predetermined time. .
  • the measurement of SaO 2 and the number of beats is performed every 1 second, and their IC card (102) is recorded every 5 seconds.
  • the time is written in the IC cart (102) every minute.
  • the operation of the data memory step in this case is shown in FIG.
  • Sa0 is Menoka c te was to determine whether the serial use the data and time of 2, and the like.
  • ALF is a flag in which each bit shown in Table 1 is set to "1" according to the alarm concept and the "undefined”.
  • DNF is a flag indicating whether it is carboxymethyl in IC card to the third power sale to Sa0 2 and what data is specific time other than pulse rate number by shown in the table below (1 0 2).
  • a flag (DNF) is set at a predetermined address of the IC card (102).
  • the addresses (AD) and (ADR) of (102) are made equal. Then, the flag (D f NF) at # 4 0 1 "0 0 H " to be set. Then, “1” is added to the counter (TDM) at # 402, and at # 403, it is determined whether the count value of this counter (TDM) is less than “5”. I do. If the count of the counter (TDM) is "5" or more, the count value is set to "0" in # 404 and the flag (ALF) is set in # 405. Set “0 0 H.” Here, when the force point value of the counter (TDM) becomes “5” or more, it indicates that the condition has deteriorated for 5 seconds.
  • the cause of the measurement failure is determined in # 403 to # 415, and according to the cause,
  • the flag (ALF) is set. This operation is similar to steps # 304 to # 310 in FIG. Then, "# 2" is added to the memory address (AD) of the IC card (2) at # 416. This is to set the address of next data to be used in addition to the flag (ALF) (DNF).
  • the S a0 2 lower Medogi Tsugechi is Ki ⁇ note to re address (AD) of the IC card (2), # 4 3 1 a flag with even flag (DNF) and (DNF) - "0 1 H "
  • the OR signal for each bit is set, and "1" is added to the memory address (AD) of the IC * mode (2) in # 432.
  • the flag (DNF) and the OR signal for each bit of the original flag (DNF) and "01H” are set, and the fighter between Table 3 and Table 3 is described in Table 1.
  • step # 23 a data damping step is executed.
  • the dedicated printer (104) is connected to the main unit (1'03), and the IC card set in the main unit (103) is assumed. Only when the dedicated link (104) requests the main body (103) to output a series of data recorded in the device (102), the IC force (102) is output.
  • the series of data described in (1) is output to the dedicated printer (104) via the CPU (110) and the input / output unit (116).
  • the number of beats display section (158) displays the time until the printing of the series of data is completed on the dedicated printer and (104).
  • intermittent measurement mode it is determined whether or not the mode is set to an intermittent measurement mode (intermittent measurement mode).
  • intermittent measurement mode it is measured with Sa0 2 and pulse rate of the same patient over time, used to also save power when there is no need to measure the communication ⁇ .
  • intermittent mode The mode is executed when the intermittent mode switch (not shown) provided in the main body (103) is set to the ON state.
  • the program jumps to ⁇ , and the operation of each unit is repeatedly executed according to the above flow. If it is set to intermittent mode, you will be asked if you want to proceed to # 25 to renew your location.
  • the calculation and display of the number of beats may be performed by causing only (121) to emit light.
  • the CPU (110) operates in the normal operation mode.
  • the oximeter body (103) of this embodiment is used for both spot measurement and continuous measurement.
  • the probe identification output unit (124) of the probe ⁇ - (101) is used for spot measurement or continuous measurement.
  • Information that can be distinguished is set.
  • the discrimination of the sake determination mode by the probe (101) is set as binary information by a switch or the like.
  • Their to measure Potan (not shown) is emitted by each LED only when pressed, is calculated Sa0 2 and the number of dark beats, are displayed and outputted.
  • the CPU (110) is in the normal measurement mode, and in # 33, RLED (120) and IRLED (122) are driven by the above driving waveform. It emits light, and the same A / D conversion processing step as in # 12 is executed in # 34, and the SVR and SVIR are obtained. Then, in # 35, it is determined whether or not the number of samples is not " ⁇ ".
  • S a0 2 Liu Tei ⁇ is compared with the previous S a0 2 3 ⁇ 4 Tei ⁇ , as its difference is stable if within Tatte a predetermined given time, at that time in # 4 2 Hold the display of the Sa0 2 child and the pulse number plant of the present.
  • a detailed box of this SaO 2 stable separate step is shown in the flowchart of FIG.
  • # 4 2 holes display of S a0 2 value and pulse rate value at that time in sul.
  • the display is held by judging the stability of SaO 2 , but the stability may be judged by the pulse rate, and the stability of the lake constant may be judged in the same manner.
  • FIG. 41 shows a flowchart showing the operation of the two-step output of the step a.
  • the CPU (llO) sends a print command to the dedicated printer (104) via the input / output unit (116).
  • the data set end signal (FFH) is output in # 601, and in # 602, the "year”, “month”, “day”, “hour”, and “minute” of the clock section (118) are output. Is gradually output via the input / output unit (1 16).
  • the flag (DN) is set to "2" in # 603. This indicates that two data, "month and day” and "hour and minute” were output.
  • step # 46 determines whether or not the spot measurement is to be performed.
  • the process returns to # 31, but if the sake brewing mode has been changed, the process proceeds to # 47 to run the CPU (1110) in the operation mode. Set to and jump to I.
  • the probe identification output section (124) is provided in the probe, but a means for setting whether to perform the robot measurement or the continuous measurement may be provided in the main body (103).
  • the volume of the tonal sound can be reduced by pressing the up-down switch (1 ⁇ 4) while pressing the pulse switch (178). Furthermore, generation of that sound and its stop can be switched by pressing the pulse switch (178).
  • Fig. 43 conceptually shows the configuration of the dedicated printer (104).
  • Fig. 4 3 In (181) data input / output ⁇ is used to receive data from the main unit (103) and to transfer instructions and the like to the main unit (103).
  • the control section controls the entire printer.
  • (184) is a switch input unit for reading the state of each switch described later.
  • the printer control unit activates the printer in accordance with the driving command and data from the control unit (183).
  • (186) is a printing unit for performing printing.
  • FIG. 44 shows the operation unit of the printer (104) of this embodiment.
  • (188) a feed switch, (188) a bullet switch, (189) a data dam switch,
  • (190) is a data interval selection switch.
  • Fig. 45 shows the operation flow of this printer.
  • # 800 it is checked whether a print command has been sent at the digital output 2 step of # 43 shown in Fig. 31 showing the operation of the main unit (103). Jumps to V when is sent. If the print command has not been sent, the print switch (188) or the data dump switch (1) of the switch input section (184) is output at # -8-801. It is known whether or not 8 9) is pressed.
  • the print switch (188) When the print switch (188) is depressed, it proceeds to # 803 through # 801 and # 802, and from the printer (104) to the main unit (103). To send a charge stop signal.
  • the printer (104) sends a charge stop signal to the main unit (103) from immediately before the start of the stamp to the end of the stamp.
  • the charging of the NiCd battery in (103) is stopped during that time. Further, the control unit (183) immediately issues a command to the data input / output unit (181) to receive data from the main unit (103). And # 8 0 Enter the patient name "NAM" at 4 and enter the patient ID number "IDN O.” at # 805. Then, at # 806, the printer
  • the data input / output section (181) of (104) is a set of digital output from the main body (103) in one step (Fig. 31 # 20 and Fig. 38). Receive the data of. Its to, in control ⁇ (1 8 3) # 8 0 7, the received data Ri by data "year”, “month”, “date”, “time”, “minute”, “Sa0 2", Enter the "number of beats", "information on alarm status", "patient ID number”, etc., and return to # 800.
  • control unit (183) of the printer (104) receives the data transferred at # 809: the data is received, and at # 810, the data is transferred from this data to the fourth unit. It is converted to the graph shown in the figure, and the print command is transmitted to the printer control »drive unit.
  • the print unit (186) prints it with # 811 # 1.
  • this de-interval selection switch (130) can be manually operated to defeat "5 sec”"10sec", It is set to one of the indicators of "1 iin” 5 ⁇ ⁇ ⁇ ", and the time for the combined index is set.
  • the printer Immediately before printing starts, the printer outputs a charge stop signal to the main unit (103), and resets the charge stop signal when printing is completed.
  • the printer When printing is completed, it is determined whether or not the data has been completed in # 812. If all the data has been printed, the process jumps to the start. If the data printing has not been completed, return to # 808 to start data reception again and repeat the same process.
  • the display of the main body (103) In the data dump mode, (1), the display of the main body (103)
  • FIGS 4.7 to 49 show more detailed charts of the operation of the special-purpose printer (104).
  • Ube 186 of the dedicated printer (104) is a doll "., *" In which the heads of the eight swords are arranged in one row.
  • the data dump mode Every 5 seconds from the data every 5 seconds returned to the IC card (100.2), the data interval is selected, and the selection switch (130) is set.
  • the data is bit-upd every 0 seconds, 1 minute, or 5 minutes, and the bit-up data is 8 bits equal to the number of print heads.
  • I Information on whether or not the vent marker switch has been pressed is stored in the flag (ALF) of the IC card (102).
  • # 9000 it is determined whether or not an input command has been received from the input / output unit (116) of the main unit (103), and if it has been received, the process proceeds to # 903. If no data has been received, the process proceeds to step # 910, and it is determined whether or not the data dumb switch (189) has been pressed. Then, if this data dump switch (183) is pressed, jump to # 3332 in Fig. 48. If it is determined that the data dump switch (189) has not been pressed at # 301, then proceed to # 902 to determine whether the print switch (188) has been pressed. Is determined. If the print switch (188) is not pressed, the flow returns to # 300. If the print switch is pressed, the flow proceeds to # 903.
  • a charge stop signal to stop charging the NiCd battery of the main unit (103) is sent to the main unit (103), and at # 904, the main unit (103) is charged. Input the data output from. Then, in # 905, the input data waits for the data set end signal (FFH), and the data set end signal (FFH) is set by step # 3334 in the main unit (103). When) is input, the process proceeds to # 906. In # 306, data of "year”, “month”, “day”, “hour”, and “minute” are received from the main unit (103), and in # 307, main unit (103) is received. The output indicating the used 7 lags (ALF) from is recorded in the memory address (DN 2) of the memory section (182). Further, in # 908, the data written in the memory address (DN2) and the key for each bit of "F0H” And record it at the memory address (DN 3).
  • this # 309 it is determined whether or not it is in a state where it is not possible to establish a link.
  • the character “ ⁇ ” is printed along with each patient's data.
  • the recording data of the memory address (DN 3) is “0 0 If it is not H ", it is impossible to measure. Therefore, the cause of the unmeasurable state is determined from the memory address (DN 3) famine in # 32, and # 92, # 32 The cause is determined by 6 and # 3 27. If the cause of the indeterminate alcohol condition is “C” due to the disconnection of the connector, “INOPC” is determined by # 32 8 If the cause is "L” due to insufficient light, enter "1 1 ⁇ 0 L" in # 3 23. Further, measurement failure ⁇ may be caused by finger movement.
  • a data transfer instruction is sent from (104) to the main unit (103), and a flag (DNF) data is received from the main unit (103) at 1001. And, in # 1002, this received flag
  • the data of (D N4) and the data of the flag (D N5) are added, and this is newly classified as a flag (D N4). Further, in # 1007, the data of the flag (DNF) and the AND signal for each bit of "80H” are calculated, and it is determined whether or not the result of the calculation is "0H". I! Separate. If the result of this operation becomes "0H”, "2" is added to the data of the flag (DN4) at # 1008, and a new flag is added.
  • a data transfer instruction is sent from the dedicated printer (104) to the main unit (103).
  • the data set entered in # 9337 is entered in the recording section (182), and # 9338 indicates whether the entered data indicates a measurement inability Is determined. If it does not indicate that measurement is not possible, the SaO 2 measurement data entered in # 9339 Calculates and sets the position of the print head to be printed, and sets the number of beats entered using # 9 4 0. And set it, then go to # 942. On the other hand, if it is determined that it is undeterminable, set the corresponding print head so that it will not be turned on in # 941, and set "1" from the flag (CD) data in # 3342. "Is decremented and newly classified as a flag (CD).
  • the time interval selected by the data interval selection switch (130) is 5 seconds, 10 seconds, 1 minute, or 5 hours. The minutes are separated.
  • the time interval is selected to be 5 seconds, it is determined whether or not the data of the flag (CD) is “0” in # 346.
  • the data of the flag (CD) is not "0"
  • the flow returns to # 336.
  • the time interval is selected to be 10 seconds in # 944, set the flag (CDP) to 1 in # 361, and use # 9662 to set the data set input route shown in Fig.49. Run the chin. Then, at # 3663, "1" is subtracted from the data of the flag (CD ⁇ ), and at # 9664, whether the data of the flag (CD ⁇ ) is "0" or not! ! Separate. Then, in # 364, it is determined whether the data of the flag (CD #) is "0" or not, and if it is not "0", the process returns to # 344. Therefore, the flag (CD #) is set to "0".
  • the oximeter system of this example When measuring the oxygen saturation of the arterial blood of the patient, the set value is recorded in a non-volatile storage means attached to the main body, so that the brewer can use the brewer's plant every time.
  • This eliminates the need for recording, and reduces the need for continuous measurement, and also eliminates the need for the main body used for measurement to have the function of analyzing the measurement element, and is therefore small and small. Suitable for lake setting. Therefore, according to the present invention, it is possible to provide a non-invasive oximeter which is suitable for both measurement and robot measurement. Further, according to the oximeter system of the present flag example, it is possible to easily analyze a large number of interpolated data in real time or after the measurement is completed. You.
  • Fig. 50 shows the data analyzer (C) shown in Fig. 5 in a more detailed box.
  • the data analyzer (C) is connected between the serial-parallel exchange unit (31) and the arithmetic control unit (35). 14 parts (200) and an image processing part (201) and an image recording part between the display part (37) and the arithmetic control part (35).
  • the image recording unit (202) has a matrix-like notation system corresponding to each pixel of the display unit (37). Writing is performed from the arithmetic control unit (35). This is performed according to the command sent to the management unit (201).
  • the memory mounting part (203) is a part for mounting the memory in which the data measured by the oximeter body (A) is written.
  • the operation modes of the data analyzer (C) include a real-time mode and an analyze mode. This mode is selected by the R button (43) or the A button (44) in the control section (36).
  • Fig. 51 is a flow chart of a series of operations performed when the electric field is turned on in the data analysis (C). In # D1, initialization of the computation-controlled area (35), image processing section (201), printer section (38), etc. Is performed. In # D2, it is determined whether the mode is the analysis mode or the real-time mode. This ⁇ is A button
  • step # D2 If it is determined in step # D2 that the A button (44) has not been pressed, the operation proceeds to step # D4 to perform the processing in the real-time mode, and then returns to step # D2.
  • Figure 52 shows the flow chart. First, in # D10, the oximeter body
  • a data transfer command is sent to (A).
  • the data is stored and recorded in the storage unit of the oximeter body (A). Therefore, when the data from DNF to one byte before the next DNF is regarded as one data set The difference in the number of bytes comes out. Therefore, in the all data reception routine of # D11, the S value of the data set is kept constant and the data is written to the storage unit (200). That is, in the all data reception routine of FIG. 54, the input of the data set is performed in accordance with the aforementioned flowchart of FIG. 43 at # D20.
  • the data group length is a maximum of 3 bytes as shown in Fig. 53. For DN4 calculated by # D20,
  • DN 4 Number of data (including DNF)-1 to (32) holds, so to unify the data group length, write "0 0 H” for (8-DN 4) in # D22. ⁇ ⁇ Insert into the part (200).
  • This data group length does not extend to 9 bytes, and can be changed according to the way of using the oximeter body (A).
  • # D23 it is determined whether or not all data has been transmitted, and if all data has been transmitted and if not a data end, # D20 is entered. Returns and repeats until all data has been sent. When the transmission of all data is completed, the process returns to # D12 in FIG. 52 to disable data reception. As a result, no new data is sent even if the oximeter body (A) returns to the normal state, so the data analyzer (C) alone can analyze the data. You can do it.
  • #D 13 is a loop of the analysis process. The loop is executed until the R button (4 3) is pressed, and the process is skipped if the R button (4 3) is pressed. Move on to
  • FIG. 55 is a flowchart showing a detailed operation of the analysis processing loop of FIG. 52 # D13. The operation will be described below.
  • # D30 to # D37 are initial screen displays. Screen S a0 2 of graph display, Warabi beats of graph display, heat scan is from preparative grams etc. are summer, S a0 2 graph display unit and a to example 5 6
  • FIG pulse ⁇ graph display unit Set the display area of 500 X 600 pixels like this.
  • the horizontal direction is defined as the i-coordinate as shown, and the ⁇ 3 ⁇ 4 direction is defined as the j ⁇ target. It is assumed that the S aO 2 display section (a) has about 200 ⁇ 600 pixels and the karyo beat display section (b) has about 300 ⁇ 600 pixels.
  • ESC Escape flag In Table 4, “Dyspinter” indicates the interval at which points are displayed on the screen, and “ModeO” prints dots every 50 pixels. In this case, 12 data will be inserted on the extra side, and since the time between the sake determination data is 5 seconds, data of 5 seconds X 12-60 seconds is displayed. . The same applies to other modes. In “Mode l”, “Display lnterval” is 10, so 5 minutes of data are displayed on the full screen, and in “Mode 2”, 10 minutes of data are displayed on the full screen. In “Mode 3”, 50 minutes of data is displayed on the full screen,
  • Data Interval in Table 4 is, for example, "Mode 4" because the number of pixels in the time sleeve ( ⁇ ⁇ ) direction is 600 with respect to the data number of 1200. This is a parameter for extracting and displaying 600 data by subtracting data every other data. Therefore, it is not necessary to thin out in the mode of “number of data pixels”.
  • the cursor position S indicating the cursor position S (hereinafter referred to as C.C.) is set to "300" in the center of the screen.
  • the vertical sleeve scale is initialized. ⁇ Sleeve scale: 3 & 0 2 display: 50% 100%, 80% ⁇ : 100% 2 steps, pulse rate display: 20 bp 25 0 bp 50 0 bp 150 bp 100 bpa 250 bpa can be specified from among three levels, which are selected by operating the first scale button (47) and the second scale button (48), respectively. Table 5 shows the parameters for setting the sleeve scale.
  • the offset is used to calculate the display coordinates. It shows the lowest value (5 O bpe in “S a0 2 5 0 1 0 0” mode) in the parameter in mode.
  • # D 3 3 sets the initial mode to “S a0 2 5 0 Z 1 0 0 mode ", and" PR 2 0 Z 2 5 0 " is set to mode, for determination of di spray routine to be described later, their respective" S a0 2 S cale 1 flag "” Set the PRS ca 1 e 1 flag ".
  • Head Address indicates the first address where data is recorded.
  • the initial screen display i.e. S a0 2 graphs Display, pulse rate 'graphical display, cursor display, digital It displays a priest and a histogram. Details of this display routine will be described later.
  • a button input is accepted with # D38.
  • the screen can be moved left and right with the first and second cursor buttons (50 and 51) shown in Fig. 6. it can.
  • the digital plant display shows the position indicated by the cursor.
  • the MZ R button (52) is a button for moving the graph so that the cursor position is lost in the screen. it can.
  • the enlargement button (53) and the reduction button (54) are used to enlarge and reduce the image centering on the center of the screen in the five-stage port shown in Table 4.
  • the first scale Pota emissions (4 to 7) is changed over to the jar good of Table 5 the scale Lumpur S a0 2 in two stages, the second scale port Tan (4 8) the first the scale number of ⁇ Return to 3 stages as shown in Table 5.
  • the print button (55) is pressed, a hard copy of the screen is performed, and the analysis screen can be printed.
  • Fig. 57 shows the flow chart of button input.
  • the flag that indicates the screen color in the analyze mode is “Sys tea Flags”. I do.
  • Table 6 shows the details of the "System Flags”.
  • # DB1 clears all "Syste ⁇ F1ags”.
  • #D] B2 check whether the R button (43) was pressed. If it was pressed, set the Escape flag in # DB3 and set # D39 in # 55. Go. # If the 1 button (4 3) is not pressed at 0 82, move to Ritsu DB 4, and check if the MZ R button (5 2) is pressed. If so, # MZR flag at DB 5 And proceed to DB6 as it is if it is not pressed.
  • # In DB 6 check whether the large button (53) has been pressed. If not, move to # DB 9. # 0 8 6 presses the large button (5 3). For example, go to #DB 7 and check “Mode Nuber”. This “Mode Nuber” corresponds to “Mode” in Table 4. If it is 0, it is “Mode 0”. If not 0, move to #DB 8 and destroy one "Mode N ueber" o
  • # DB9 it is checked whether the reduction button (54) has been pressed, and if not, the process proceeds to # DB12. # If the reduction button (5 4) is pressed at D B 9, at # B 10
  • Mode N uaber is called. If there is 4, go to # DB1 2 and if it is 4, go to # DB1 1 and I "
  • the PRS ea lei flag is set in #DB 16; If it is not in “PR 20/250” mode, it is determined in # DB17 whether it is in "PR 50/150” mode. If it is in "PR 50/150” mode, it is DB Set the PRS cale2 flag in 18 and set the PRS cale 3 flag in # DB19 if not in the "PR 50 150" mode.
  • # In DB20 it is determined whether or not the first cursor button (50) has been pressed. If the first cursor button (50) has been pressed, proceed to # DB21 and proceed to the first DB. Raise the cursor flag and move to # DB22 if it is not pressed.
  • # DB 22 determines whether the second cursor button (5 1) has been pressed, and if so, sets the second cursor flag #DB 23. Here, if the second cursor button (5 1) is not pressed, the process proceeds to #DB 24, and it is determined whether the print button (55) is pressed. For example, set the Print flag at # DB25, and if it is not pressed, exit the button input routine and return to # DB39 in Fig. 55. Referring back to FIG.
  • D l sp l ay In terva 1 t-(36) is calculated.
  • # D42 after moving the graph by operating the MZR button, set the cursor counter C.C. to "300" to move the cursor position to the center of the screen. I do.
  • the process proceeds to # D49 to determine whether the second cursor flag is on. If the 2nd cursor lag is not on, Proceed to # D5 5 with * to move to the display. Here, if the second cursor lag is on, change the cursor cursor C .. to move the force cursor to the right, but if the cursor is on the right side of the screen * Stop one sol and shift the graph itself to the left. Hayashi If the second ⁇ —sol flag is on D 49, proceed to #D 50,
  • Figure 58 shows the flowchart of this routine.
  • Yokosuke's index i is set to 300 at # DD18.
  • set DNF AD "C enter Data”
  • # DD20 set "Scan counter” for data scanning.
  • Fig. 59 is a flow chart of the above algorithm.
  • the address next to the address DNFAD is checked at # DC1, and the setting is not possible at the holly DC2 (IN 0 P ).
  • the content of the address DNFAD + 1 is ALF indicating the alarm status, and Table 1 shows the meaning of each bit.
  • DNFAD head address (Head Address) of the recording data. If it is not the head address, the process goes to # DD28 and checks whether "S can Counter” is 0. If not 0, return to # DD25 and repeat the operations from # DD25 to # DD28 again. # If "Scan Counter” is 0 in DD 28, #DD 29 is 9 bytes of data from the DNF AD address at that time It performed Detachi click of the 5 9 FIG illustrated for the set, # DD 3 0 at the calculated js, the next display coordinates from jp (I sao 2 2, J sao 2 2) (I pr2, J pr2) Ask for.
  • # DD 5 2 ⁇ # DD 5 was Motoma' at 6 (I sao 2 1, J sao 2 1) (I sao 2 2, J sao 2 2) (I pr 1, J pr 1) (I pr 2, J pr 2) Complement the line and display it. From # DD57 to # DD62, if DNFAD becomes the address of the DNF in the Shin-end set, all parts between ⁇ and 600 at that time are turned off. In # DD63, the DNFAD at that time is noted as LDNFAD, and used for drawing a histogram later described. #DD 6 3 Sa0 2 ⁇ Pi ⁇ number until is displayed graph, the horizontal sleeves in accordance with the shaved Lumpur graph in # DD 6 4, for displaying the ⁇ .
  • Fig. 60 shows the detailed flowchart of the Fig. 58 # DD65 cursor digital plant display routine. ⁇ One sol has various shapes, but in this embodiment, it is indicated by a straight line that cuts off the screen. In Fig. 60, # DCD 1 is the point of the previous cursor.
  • the sentence display instruction can be realized by sending its coordinates, sentence code and sentence display instruction to the image processing unit (201). If the measurement is impossible (IN0P), the cause of the indetermination (IN0P) can be found by examining the contents of the address DNFD + 1, and the cause can be displayed on the screen in text. For example, from Table 1 above,
  • the pulse wave is weak, indicating that the measurement is not possible, so the letter "P" may be displayed.
  • the data set contains information such as Sa0 2 and ⁇ beat rate, upper warning 100%, pulse rate lowering warning ⁇ , time, etc., these can be displayed simultaneously. It is.
  • each frequency memory is first cleared with # DH1.
  • # DH 1 in 6 to # DH 2 4 determines the data has been made, for example, pulse ⁇ is 2 0 0 bp ⁇ of i5 # DH 1 6, # DH 1 8, # DH20, # DH22 # DH24, and the contents of the frequency memory PR200-250 are incremented. Then, when the number of beats is completed, go to # DH25 and add 9 to the histogram pointer Q to point to the next DNF address.
  • # DH26 is equal to or less than LDNFAD, return to # DH3 and repeat the data discrimination, and repeat the above operations until Q> LDNFAD.
  • the frequency distribution of data for the display screen is stored in each frequency memory.
  • (S aO 2 5 0 — 6 0) indicates the content of the frequency memory S a0 2 5 0 — 0, and k is a variable for indicating the size of the entire histogram in din. It is.
  • the two points (iH jHJ H jH are obtained by the calculation of equation (41), so the coordinates of these two points and the width of the graph) and the line instruction are transferred to the image processing unit (201 ) Can be used to display a histogram.
  • the image processing unit (201) sends a command to the image processing unit (201) to send data for one line of the image recording unit.
  • the image processing unit (201) sends the data of one line ⁇ to the storage unit (200) through the operation control unit (355).
  • this one line of data is transferred to the printer section (38), and one line is printed. This operation can be repeated over the entire screen to perform hardcopy of the rooster face.
  • the liquor measurement data is stored in a removable memory such as an IC card on the oximeter body, the same analysis can be performed by attaching the IC card to the data analyzer (C).
  • a removable memory such as an IC card on the oximeter body
  • Control is performed so that data is written from (203) to the memory (200).

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Abstract

Des informations sur un organisme vivant, telles que le degré de saturation d'oxygène dans le sang artériel et le pouls, mesurées par un oxymètre, peuvent être enregistrées avec des informations sur le temps de mesure dans un dispositif à mémoire, tel qu'une carte de circuits intégrés, séparable de l'oxymètre proprement dit. Lorsque le dispositif à mémoire est séparè de l'oxymètre proprement dit et relié à un analyseur de données indépendant de l'oxymètre, les informations enregistrées concernant l'organisme vivant peuvent être analysées par l'analyseur de données et les résultats de l'analyse peuvent être représentés par un graphique. Lorsqu'une imprimante indépendante de l'oxymètre proprement dit lui est attachée, les informations concernant l'organisme vivant ayant fait l'objet de mesures peuvent être imprimées. En outre, lorsqu'une unité de transmission d'une unité télémétrique est reliée à l'oxymètre, et une unité est reliée à l'analyseur de données indépendant de l'oxymètre proprement dit, les informations concernant l'organisme vivant mesurées par l'oxymètre peuvent être transmises par transmission sans fil à l'analyseur de données.
PCT/JP1986/000342 1985-07-05 1986-07-03 Oxymetre et systeme d'oxymetrie WO1987000027A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
JP60148548A JPS628738A (ja) 1985-07-05 1985-07-05 オキシメ−タ
JP60/148548 1985-07-05
JP61/62986 1986-03-19
JP61062986A JPH0732767B2 (ja) 1986-03-19 1986-03-19 オキシメータ

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WO1987000027A1 true WO1987000027A1 (fr) 1987-01-15

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Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0346685A1 (fr) * 1988-05-31 1989-12-20 Sharp Kabushiki Kaisha Un appareil ambulatoire d'électrocardiographie
EP0650742A1 (fr) * 1993-10-29 1995-05-03 Michael A.J. Dietl Méthode et appareil d'opération d'un défibrillateur
US5433702A (en) * 1990-06-14 1995-07-18 Opthalmocare, Inc. Phaco handpiece providing fingertip control of ultrasonic energy
KR20020033038A (ko) * 2000-10-27 2002-05-04 박헌철 목질 칩을 미생물 담체로 하는 탈취 장치
US9375185B2 (en) 1999-01-25 2016-06-28 Masimo Corporation Systems and methods for acquiring calibration data usable in a pulse oximeter
US10231676B2 (en) 1999-01-25 2019-03-19 Masimo Corporation Dual-mode patient monitor

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5088873A (fr) * 1973-12-10 1975-07-16
JPS5524004A (en) * 1978-06-22 1980-02-20 Minolta Camera Kk Oxymeter
JPS58138442A (ja) * 1982-02-15 1983-08-17 住友電気工業株式会社 経皮生体計測モニタ装置
JPS59160446A (ja) * 1982-09-02 1984-09-11 ネルコ−・インコ−ポレ−テツド オキシメータ装置
JPS6014311A (ja) * 1983-07-04 1985-01-24 Sumitomo Electric Ind Ltd 電源電圧監視装置
JPS60176624A (ja) * 1984-02-23 1985-09-10 ミノルタ株式会社 動脈血酸素飽和度測定装置

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5088873A (fr) * 1973-12-10 1975-07-16
JPS5524004A (en) * 1978-06-22 1980-02-20 Minolta Camera Kk Oxymeter
JPS58138442A (ja) * 1982-02-15 1983-08-17 住友電気工業株式会社 経皮生体計測モニタ装置
JPS59160446A (ja) * 1982-09-02 1984-09-11 ネルコ−・インコ−ポレ−テツド オキシメータ装置
JPS6014311A (ja) * 1983-07-04 1985-01-24 Sumitomo Electric Ind Ltd 電源電圧監視装置
JPS60176624A (ja) * 1984-02-23 1985-09-10 ミノルタ株式会社 動脈血酸素飽和度測定装置

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0346685A1 (fr) * 1988-05-31 1989-12-20 Sharp Kabushiki Kaisha Un appareil ambulatoire d'électrocardiographie
US5002062A (en) * 1988-05-31 1991-03-26 Sharp Kabushiki Kaisha Ambulatory electrocardiographic apparatus
US5433702A (en) * 1990-06-14 1995-07-18 Opthalmocare, Inc. Phaco handpiece providing fingertip control of ultrasonic energy
EP0650742A1 (fr) * 1993-10-29 1995-05-03 Michael A.J. Dietl Méthode et appareil d'opération d'un défibrillateur
US9375185B2 (en) 1999-01-25 2016-06-28 Masimo Corporation Systems and methods for acquiring calibration data usable in a pulse oximeter
US10231676B2 (en) 1999-01-25 2019-03-19 Masimo Corporation Dual-mode patient monitor
KR20020033038A (ko) * 2000-10-27 2002-05-04 박헌철 목질 칩을 미생물 담체로 하는 탈취 장치

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