WO1994013197A1 - Ensemble fonctionnel d'acquisition de donnees pour systeme de surveillance de patient - Google Patents

Ensemble fonctionnel d'acquisition de donnees pour systeme de surveillance de patient Download PDF

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Publication number
WO1994013197A1
WO1994013197A1 PCT/US1993/011710 US9311710W WO9413197A1 WO 1994013197 A1 WO1994013197 A1 WO 1994013197A1 US 9311710 W US9311710 W US 9311710W WO 9413197 A1 WO9413197 A1 WO 9413197A1
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WO
WIPO (PCT)
Prior art keywords
data acquisition
pod
signals
patient
signal
Prior art date
Application number
PCT/US1993/011710
Other languages
English (en)
Inventor
Bernd Rosenfeldt
Kenneth Fuchs
Thomas Kipling Naylor
Scott Newell
Original Assignee
Siemens Medical Systems, Inc.
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
Application filed by Siemens Medical Systems, Inc. filed Critical Siemens Medical Systems, Inc.
Priority to JP6514250A priority Critical patent/JPH08504344A/ja
Priority to EP94905331A priority patent/EP0673224A1/fr
Publication of WO1994013197A1 publication Critical patent/WO1994013197A1/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
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0015—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by features of the telemetry system
    • A61B5/002—Monitoring the patient using a local or closed circuit, e.g. in a room or building

Definitions

  • the present invention relates to medical systems and in particular to patient monitoring systems for collecting, storing and displaying medical data pertaining to the patient.
  • Monitoring systems in the related art have typically fallen into one of two general categories: multi-function monitoring, recording and displaying systems which process and collect all of the data desired, but are bulky and difficult to transport; and small, portable systems which are easy to transport, but process and collect fewer types of data and have limited storage capability.
  • multi-function monitoring, recording and displaying systems which process and collect all of the data desired, but are bulky and difficult to transport
  • small, portable systems which are easy to transport, but process and collect fewer types of data and have limited storage capability.
  • a patient is connected to a simple, portable monitor to observe a limited number of medical attributes, such as EKG or non-invasive blood pressure.
  • higher care facilities e.g., an intensive care unit or operating room
  • this is accomplished by disconnecting the patient from the simple monitor and connecting the patient to a monitoring system having more robust capabilities.
  • U.S. Patent 4,715,385 and 4,895,385 to Cudahy et al. discuss a monitoring system which includes a fixed location display unit and a portable display unit.
  • a digital acquisition and processing module (DAPM) receives data from sensors attached to the patient and provides the data to either or both of the fixed and portable display units.
  • the DAPM remains attached to the patient during patient transport, eliminating the need to remove intrusive devices from the patient before transport and to reconnect the devices after transport.
  • the DAPM is inserted into a bedside display unit located near the patient's bed. An electrical connection to the bedside display is formed when the DAPM is inserted into the bedside display.
  • the DAPM is first connected to the portable display by attaching a cable, and is then disconnected from the bedside display by removing it from the bedside display unit. Once the DAPM is disconnected from the bedside display, a transportable monitoring system is formed, comprising the portable display and DAPM. In order to place the DAPM in the bedside monitor, sufficient cable length is provided between the sensors and the DAPM to reach the bedside display unit.
  • the lines transmitting the analog data signals from the patient to the DAPM are long enough to reach from the patient to the bedside monitor.
  • This cable length may produce undesirable interference between the analog signals, and may allow corruption of the analog signals with noise due to, for example, radio frequency interference (RFI) from external sources.
  • RFID radio frequency interference
  • the digital acquisition and processing module of the Cudahy et al. system has a fixed parameter configuration, and if the parameter requirements change due to a change in condition of the patient, the digital acquisition and processing module must be disconnected and a different module including the new parameters which are required to be monitored must be connected. This process is not only time consuming, due to the reconnection of the sensors and cables between the patient and the module, but also destructive of data since patient data acquired in the first processing module is lost when the module is disconnected.
  • the processing module of Cudahy et al. is bulky and difficult to position near a patient.
  • the processing module of Cudahy et al. requires extensive cabling to the different patient sensors, which further adds to the complexity and set-up time of the system.
  • Another aspect of prior art data acquisition devices is that they are not standalone devices.
  • An example is the SirecustTM cartridge system manufactured by Siemens Medical Equipment.
  • Patient medical data are collected by one or more multiparameter cartridges.
  • the cartridges are inserted into a SIREMTM module box.
  • the large size of the module box makes it impractical to place the box on or above the bed; it typically must be placed beside the bed, and may get in the way of hospital personnel who are treating the patient. Not only is the box in the way, but as noted above, an array of cables between the cartridge and the patient further interferes with movement of hospital personnel.
  • the Hewlett-Packard MerlinTM system and the Marquette TRAMTM systems are similar in that they also require insertion of a cartridge into a module box to display data on a bedside monitor.
  • the Cudahy patent has a similar limitation: the DAPM must be inserted into the fixed (bedside) display to display data on that display. None of these is a standalone device.
  • Additional simplification is desired, in order to reduce the time to prepare the patient and monitoring system for transportation to an operating room or intensive care unit. Reduction in the noise and RFI in collected analog signals is also desirable. Reduction in total size of the whole data acquisition apparatus (including the module box) is desired.
  • the present invention is embodied in a data acquisition pod suitable for use in a system that includes a display.
  • the pod continually collects a plurality of analog data signals representing at least two parameters of a patient condition using a plurality of sensors coupled to a medical patient.
  • the data may be collected using the data acquisition pod while the patient is stationary and while the patient is being transported.
  • the data acquisition pod receives patient data signals representing at least two different parameters from the plurality of sensors.
  • the patient data signals are conditioned for transmission to the display device by circuitry within the data acquisition pod.
  • the circuitry is selectably locatable proximate to the sensors.
  • the data acquisition pod is a standalone apparatus, and is selectively coupled directly to the display device.
  • the circuitry may be positioned independent of the display device.
  • Figure 1 is a perspective drawing which shows two data acquisition pods in a accordance with the invention.
  • Figure 2 is a block diagram of a data acquisition pod as shown in figure 1.
  • Figure 3a is a block diagram of the EKG pod shown in figure 1.
  • Figure 3b is a block diagram of the EKG printed circuit board shown in figure 3a.
  • Figure 3c is a block diagram of the SP02 and Opto-isolation printed circuit boards shown in figure 3a.
  • Figure 4 is a block diagram of the pressure pod shown in figure 1.
  • FIG. 1 shows a system which includes two exemplary data acquisition pods 10 and 30 in accordance with the invention.
  • the pod 10 includes a plurality of terminals 14 for coupling to, EKG electrodes and a plurality of multi-function terminals 12 for coupling to resistance sensors such as temperature, nasal respiration or cardiac output thermodilution. Leads from these sensors are connected to the terminals 12 by a plurality of receiving lines 16.
  • the pressure pod 30 includes terminals 23a-23d for receiving signals from pressure transducers (not shown) , and terminals 24a and 24b for receiving signals from temperature sensors.
  • the electrodes and sensors (not shown) are attached to a patient, and remain attached to the patient and to the pod while the patient is stationary as well as while the patient is being transported.
  • the pod may be placed on a bedside table or may be attached to the bed or an intravenous pole.
  • data acquisition pods 10 and 30 are preconfigured, standalone (self contained) , multiparameter units.
  • pods 10 and 30 include all of the electronics required to receive the analog pressure signals from the sensors, filter the signals, combine them into a single multiplexed analog signal, and convert the single signal from analog form to digital form.
  • This digital output signal may be transferred directly to a display device 20 (which may include data processing functions) by wire 34 or a wireless (e.g. , infrared) link (not shown) .
  • a display device 20 which may include data processing functions
  • a wireless link not shown
  • pods 10 and 30 are neither inserted into a bulky box or rack, nor into the display device itself, to form electrical paths to the display device.
  • the data acquisition pods are independently positionable because they are standalone devices. Using the data acquisition electronics described below with reference to Figures 3a, 3b, 3c and 4, pods 10 and 30 may be formed in small enough packages to be conveniently placed in a variety of locations in close proximity to the patient. Reduction is size is all the more important where, as in pods 10 and 30, multiple medical parameters are monitored by a single pod.
  • the data acquisition pod is selectively and detachably coupled by a single coupling line 18 to a display 20, which may be a portable display. If for any reason, it is desirable to replace display 20 with a further selected display (not shown) , this is accomplished by detaching a single coupling line 18 from the old display, and attaching the line 18 to the new display.
  • a data acquisition pod 30 is also shown.
  • Pod 30 is adapted to receive data representing blood pressure or both pressure and temperature.
  • the EKG Pod 10 and the pressure pod 30 each include aspects of the invention, they may be used in combination with one another in a data acquisition system, as shown in figure 1.
  • Pods 10 and 30 may be independently with respect to from each other and to the display 20. Pods 10 and 30 are small enough in size to be conveniently located close to the patient.
  • the electrical path between the patient and the pod, as determined by the length of the receiving lines 16 to which the sensors attach, is substantially less than the length of coupling line 18 or 34 which couples the pod to the display 20.
  • a data acquisition pod 10 or 30 constructed in accordance with the circuit descriptions which follow is compact enough to be collocated with the sensors. EKG pod 10 may be placed on the bed adjacent the patient, and the pressure transducers (not shown) may be mounted on pod 30 by inserting them in the channels 38 of the housing of pod 30.
  • the detachable coupling between the data acquisition pod 10 and display 20 is intended to include any manner of communicating the acquired data signals to display 20, such as a wireless communication link (not shown) , which may be an infrared link.
  • FIG. 2 shows a block diagram of an exemplary data acquisition pod 11.
  • Ppd 11 performs functions which are common to both the EKG pod 10 and the pressure pod 30 shown in figure 1.
  • the pod 11 receives patient data from a plurality of sensors 410a-410n. Sensors 410a-410n may be a subset of the sensors attached to the patient. These sensors may measure EKG, blood pressure, pulse, temperature, EEG or other physiological parameters.
  • Each input data stream is filtered to remove noise and any undesirable signals (e.g., radio frequency (RF) distortion) which the sensors may acquire.
  • the filtered signal is amplified.
  • the filtered output signals 420a-420d are combined to form a single signal. This combining may be performed by a time division multiplexer 414.
  • A/D converter 412 includes a single data communications coupling 19 to display 20. This coupling is through a communications application specific integrated circuit (ASIC) 416.
  • ASIC application specific integrated circuit
  • Pods 10 and 30 may include all of the functions of the pod 11 shown in figure 2. The data provided by each sensor that is coupled to the pod 11 may be sampled at a respectively different rate.
  • the multiplexer 414 is controlled by a control means 430, to provide a clock signal and to sample the analog signals associated with each respective sensor during at least one time division in accordance with its respective assigned sampling rate. Data representing each of the sensors' output signals is included in a single time division multiplexed output signal 415 during a fraction of the time divisions. In this manner, all signals may be conveyed on a single line, each at its desired sample rate.
  • the lines 16 between the patient and the pod 10 are short, while the coupling line 18 between the pod 10 and the display 20 is long.
  • This configuration shortens the electrical path traveled by the analog signals between the patient and the analog filter/amplifiers 418a-418n.
  • the noise added to each signal prior to amplification is reduced by shortening the electrical path over which the signal travels before amplification. Noise and signal transport artifacts are avoided, which would otherwise occur if the amplification were performed further from the patient and the impedances of the couplings to the patient were imbalanced. Interference is further reduced by the electrical isolation provided in the pod 10 for the EKG circuitry by way of reducing the capacitance between the signal conditioning circuitry and noise sources remote from the patient.
  • the room may have an electrical field gradient (e.g., due to lighting or to electro-surgery units). If line 16 were very long and pod 10 were placed near monitor 20, far from the patient, this field gradient could cause a significant difference in the potential between the patient and the pod. Current would flow between the pod and the patient. If the electrodes have identical impedances, this would be a common mode current which could be eliminated by differential amplification. If, however, the electrode resistances are different from one another (as is typically the case) , there is a differential voltage component between the electrodes. This differential voltage would be amplified and become noise in the EKG waveform.
  • an electrical field gradient e.g., due to lighting or to electro-surgery units
  • pod 10 is close to the patient and a low capacitance isolation is provided within the pod, isolating the circuits coupled to the patient from the circuits coupled to monitor 20.
  • the signals are converted to digital form in A/D converters 412a-412n before being transmitted across the comparatively long coupling line between the pod 11 and the display 20. Once converted to digital form, the data are less vulnerable to corruption due to crosstalk between signals and RFI.
  • a non-volatile memory device 432 is included in pod 11.
  • Memory 432 may be a conventional electrically erasable programmable read only memory (EEPROM) .
  • Memory 432 may store patient demographic data, alarm limits for the sensors, and patient trend data. By storing these data in pod 11, exchanging equipment (e.g., substituting another display for display 20) is simplified.
  • Pod 11 may be disconnected from display 20 and reconnected to another display without the need for time consuming data downloads from display 20 to the other display.
  • the memory may be a distinct memory device 434 located outside of the housing (as shown in phantom) of pod 11, and may be connected to pod 11. Memory 434 is selectively detachable from pod 11.
  • a single memory 434 is shown coupled to sensor 410n and filter 418n. Similar memories may be coupled to each sensor. If each sensor has a respective memory 434, it is convenient to allow the memories 434 to accompany the sensors when the patient moves. Thus, if a department does not wish to allow its pod 11 to accompany the patient to another part of the hospital (e.g., out of a concern that the pod will not be returned) , memory 434 may be detached from pod 11 and may be connected to another pod for transportation to a different part of the hpspital. This provides an additional element of flexibility in selectively coupling pods 11 to display 20.
  • FIG. 3a is a block diagram showing the circuitry which forms the EKG data acquisition pod 10.
  • the basic pod configuration includes three printed circuit boards (PCB's) : the EKG PCB 100, the SP02 PCB 200 and the opto-isolation power board 134.
  • the EKG PCB 100 includes circuitry for receiving and processing EKG and temperature signals, where the temperature signals may represent respiration or cardiac output data.
  • the opto-isolation power board 134 ensures patient safety by providing a power source and a return circuit for the EKG PCB 100 which are separate from return circuit used by the rest of the sensor systems.
  • the SP02 PCB 200 receives data from blood oxygen saturation pressure sensors, and handles communications between the pod 10 and the display 20.
  • Additional PCBs 280 and 290 may be provided for collecting, respectively, electroencephalogram (EEG) data on one hand and transcutaneous oxygen and carbon dioxide pressure (TCP 02/C02) data on the other.
  • Figure 3b is a functional block diagram of the EKG printed circuit board PCB 100 of the pod 10.
  • the EKG PCB 100 includes circuitry for receiving and processing data from five EKG electrodes (102, 104, 106, 108 and 110), two cardiac output thermistors or nasal thermistors, and two body temperature thermistors.
  • the EKG PCB 100 includes filters and amplifiers (112, 114, 116, 118, and 120) for processing the EKG signals received from each respective electrode. Conventional signal processing algorithms are applied to the signals from these electrodes, which are well known in the art.
  • an EKG lead is formed by comparing the voltage difference between two electrodes.
  • the output signals from the five filter/amplifier circuits (112, 114, 116, 118 and 120) are multiplexed in multiplexers 122 and 124, and are provided to differential amplifier 128.
  • seven EKG signals are derived from a selected seven pairings of the five electrodes (102, 104, 106, 108 and 110) .
  • the output signal 123 from multiplexer 122 is stored in buffer 126, and a delayed signal 127 is provided by the buffer.
  • the output signal 123 from multiplexer 122 is also provided to differential amplifier 128.
  • the differential amplifier receives input signals
  • the differential amplifier 128 subtracts signal 125 from signal 123, forming an EKG lead signal 129 from the two electrode output data signals 123, 125.
  • the output signal 129 from differential amplifier 128 and the output signal 127 from buffer 126 are provided to multiplexer/analog-to-digital (A/D) converter 130.
  • Multiplexer 122 also receives input signals from temperature sensors 150, 152, 154 and 156. Sensors 150 and 152 may collect two sets of body temperature data, or one set of body temperature data and one set of nasal respiration data.
  • sensor 152 may be a rapidly responding temperature sensor placed at the nose or mouth, which responds to temperature changes in the air entering and leaving the airway. The changes in nasal passage temperature due to the difference in temperature between inhaled and exhaled air are thus measured.
  • the data collected from sensors 150 and 152 are filtered by conventional filter means 160 and 162, respectively.
  • the terminals 12 may receive data representative of temperature, nasal respiration, or cardiac output.
  • Figure 3b shows a variation of the embodiment in figure 1, in which separate terminals 12a-12d receive data from two sets of sensors: temperature 150, 152 and either of cardiac output or nasal respiration 154, 156. It is understood that a further variation may be practiced in which additional terminals are provided for simultaneous collection of temperature, respiration and cardiac output data.
  • Sensors 154 and 156 are located in an Edwards-type catheter and provide cardiac output data using the thermodilution method.
  • An Edwards type catheter (not shown) is used to inject either cooled or room temperature water into the coronary artery.
  • An Edwards calibration resistor 158 is also located within the catheter probe (not shown) for calibrating the sensors 154 and 156. Downstream blood temperature and injectate temperatures are measured. Comparison of these temperatures yields a measurand of cardiac output, as is well known to one skilled in the art.
  • the output signals 161 and 163 from respective filters 160 and 162 are provided to a multiplexer 168, which time division multiplexes the signals together.
  • the output signal 169 from multiplexer 168 is then provided to an amplifier 172.
  • the cardiac output signals from filters 164 and 166 are multiplexed, along with the calibration signal 159.
  • the output signal 171 of the multiplexer 170 is provided to amplifier 174.
  • the amplified signals 173 and 175 are time division multiplexed together and are provided to multiplexer 122.
  • the multiplexers 122, 128 and 176 are controlled to sample signals from each sensor in .accordance with its respective sample rate. For example, EKG channels may be sampled at one hundred times the rate used for cardiac output.
  • control and clock signals 133 used to control the multiplexers are provided through an EKG communications Application Specific Integrated Circuit
  • the EKG communications ASIC 132 transfers data between the EKG PCB 100 and the opto-isolation power PCB
  • the opto-isolation power PCB 134 protects the patient by maintaining a 5000 volt electrical isolation between the
  • Figure 3c is a block diagram showing the SP02 PCB
  • the SP02 PCB includes circuitry to receive and process data from an SP02 sensor 250, which may be, for example, a commercially available sensor such as that manufactured by the Nelcor company.
  • the SP02 sensor 250 includes two light emitting diodes (LEDs) 252 and 254, which emit red and infra-red light respectively for passing light through a portion of the patient's body (e.g., an ear lobe, fingertip or toe) .
  • a photodiode 260 measures the amount of light, in particular bands of frequencies, which is passed through the patient's tissue and, thus, provides a signal representative of the relative saturation of oxygen in the patient's blood.
  • the input signal driving LEDs 252 and 254 is provided by analog mux 210 on the SP02 PCB 200.
  • a 2.5 volt reference input signal is converted to an analog signal by DAC 216 and is converted to a known current level by voltage-to-current converter 212.
  • the converter 212 provides an input signal to the analog mux 210.
  • the polarity of the 2.5 volt input signal is switched between positive and negative to alternately activate respective LEDs 252 and 254.
  • the current signal generated in the photodiode 260 in response to illumination provided by the photodiodes 252 and 254 is converted to a voltage signal 219 by a current-to-voltage converter 218.
  • This voltage signal 219 is passed through a filter 220 to cancel out components of the signal which are attributable to ambient light.
  • the remaining signal 221 is then fed through a demultiplexer which is synchronized to the mux 214, to separate the red and infra-red components of the signal, which are processed by respective filters 224 and 226.
  • a controller 215 synchronizes the operations of multiplexer 214 and demultiplexer 222, so that demultiplexer 222 samples signal 221 at the same rate that multiplexer 214 transmits signals 213. But this sample rate may differ from the rest of the components within the PCB 200. By this method, the sample rate of the returned signals 223 and 225 may differ from the sample rate of the input signals red, R, and infrared, IR.
  • the demultiplexed red 223 and infrared 225 data signals are processed by respective filters 224 and 226, and amplifiers 228 and 230.
  • the output signal 229 from amplifier 228 is multiplexed with a red reference calibration signal 257 from a reference resistor 256.
  • the multiplexed red signal 233 and the amplified infrared signal 231 are converted to digital form by respective A/D converters 234 and 236.
  • the red 235 and infrared 237 digital output signals are provided to the pod communications ASIC 238 for transmission to the display 20.
  • the opto-power board 134 provides the optional isolation between the EKG circuitry and the remaining sensors and circuits. Commands are sent from the display 20 to the EKG PCB 100 by way of line receiver 144 and opto-isolation 136. Data are returned from the EKG PCB 100 to the display 20 by way of opto-isolation 138 and line driver 146, so that the EKG return is isolated from the display ground path. Power is transferred from the display 20 to the EKG PCB 100 by way of isolation power supply 140. An EKG synchronization signal ESYNC is provided through the isolation power supply 140. The components of the SP02 PCB 200 receive commands from the display 20 (shown in figure 2) directly through the line receiver 144.
  • the SP02 PCB 200 transmits data to the display 20 directly through the line driver 146. DC power is furnished directly from the display 20.
  • a synchronization signal SSYNC (distinct from the EKG synchronization signal ESYNC) is provided to the SP02 PCB 200, as well.
  • additional sensors may be added to the data acquisition pod 10 to receive data from additional electrodes for an EEG PCB 280, or from transcutaneous oxygen and carbon dioxide PCB 290.
  • EEG PCB 280 and 290 includes filters, amplifiers, A/D converters and multiplexers to provide a single time division multiplexed (TDM) digital data output signal to the pod communications ASIC 238.
  • the EEG PCB circuits 280 use the same opto-isolation circuits and isolation power supply as does the EKG PCB 100.
  • the TCP 02/C02 PCB 290 circuits share the return, power and synchronization signals with the SP02 PCB 200.
  • the configuration of the EEG PCB 280 is as shown for pod 11 in Figure 2, except that in PCB 280, the single multiplexed output signal 19 is provided to the opto-isolation power PCB 134.
  • the output signals of the EEG PCB 280 share the same, return circuit as the output signals of the EKG PCB 100. This return path is isolated from the rest of the sensor systems.
  • PCB 134 then passes the EEG signal on to the display 20.
  • the additional terminals for receiving EEG signals may be also be used to receive data from further EKG electrodes, instead of EEG.
  • the EKG communications ASIC 132 would be modified to receive the additional EEG/EKG signals provided by PCB 280 and to provide output signals 282 and 284 to respective multiplexers 122 and 124 (as shown in phantom in figure 3b) , so that data collected from the additional electrodes is combined with data from electrodes 102-110.
  • the TCP 02/C02 PCB 290 is as shown in figure 2, except that in PCB 290, the single multiplexed output signal 19 is provided to the pod communications ASIC 238, which provides the data signals to the display 20.
  • pod 10 includes two proximately located switches 13 and 15.
  • Switch 13 is coupled to a circuit which transmits a signal to display 20 causing display 20 to start the cardiac output procedure
  • switch 13 The operator actuates switch 13 at the same time that he or she injects the injectate into the patient for cardiac output measurement.
  • the display 20 calculates the waveform of the temperature gradient between thermistors for the cardiac output procedure.
  • switch 15 is coupled to a circuit which transmits a signal to display 20 causing display 20 to configure itself to start the wedge procedure and/or switch the display to wedge mode.
  • the operator actuates switch 15 at the same time that he or she inflates a balloon inside the patient's pulmonary artery for pulmonary artery wedge pressure measurement.
  • Switches 13 and 15 are conveniently co-located on pod 10 (near the sensors on the patient) . This facilitates concurrent actuation of switch 13 while starting the cardiac output measurement, and facilitates concurrent actuation of switch 15 while starting the wedge procedure.
  • Pod 30 has a housing 36. All of the circuitry for conditioning and combining the pressure data from transducers 302a-302d is contained inside housing 36. Each transducer is connected to a hose (not shown) at the end of which is a catheter which is inserted into a blood vessel. On the outside of housing 36 are channels 38 for receiving pressure transducers 302a-302d. The pressure transducers 302a-302d slide into channels 38 and engage electrical contacts 40a and 40b to transmit blood pressure signals to the conditioning and combining circuitry within pod 30.
  • the height of the pressure pod be adjustable so that pod 30 may be placed at the height of the patient's heart.
  • Mechanical design features of pod 30, including small size and a clamping device 46 allow easy mounting on a dedicated stand (not shown) an intravenous pole (not shown) or the railing of the patient's bed (not shown) .
  • the zero switch 42 is conveniently located on pod 30, where it may easily be actuated while zeroing sensors
  • Actuating the zero switch causes pod 30 to transmit a zero signal to the display 20, causing display 20 to reset the value of its waveform to zero in response to the voltage currently detected across sensor 302.
  • a second switch 44 located on pod 30 sends a further signal to the display 20, causing display 20 to begin a wedge procedure, as described above with reference to switch 15 of pod 10.
  • the location of the zero switch 42 and wedge switch 44 on pod 30 provide the same advantages discussed above with respect to switches 13 and 15.
  • the wedge switch 15 may be actuated easily while inflating the balloon in the pulmonary artery to begin the pulmonary artery wedge pressure measurement.
  • FIG 4 is a block diagram of the pressure/temperature data acquisition pod 30 shown in figure 1.
  • the pod 30 receives data from up to four pressure transducers 302a-302d and two temperature transducers 350a, 350b. Power is provided by a single step-down power supply 310.
  • the output signals from the transducers 302a-302d are provided to respective clamping and filtering networks 304a-304d, to limit the range of the signals and remove noise.
  • the output signals 303a, 303b from each of the networks 304a-304d are provided to a differential-to-single-ended converter and 4-to-l multiplexer 308.
  • the differential-to-single-ended converter 308 generates a single signal 314 representative of pressure difference from each pair of the signals 303a, 303b.
  • a switch 370a closes and applies power to one of the sensors 302a.
  • a capacitor (not shown) within pressure sensor 302a charges up to a differential voltage which is proportional to the pressure in sensor 302a.
  • Sensor 302a has a bridge output signal which is differential in nature) .
  • switch 370a is opened again and power to sensor 302a is turned off. The voltage is trapped in the internal capacitor of sensor 302a, representing the output signal of the sensor.
  • successive switches 370b-370d are individually closed to apply power to respective pressure sensors 302b-302d in succession. This technique is known as the flying capacitor technique.
  • An advantageous aspect of this configuration is that power is conserved, relative to a system in which all four sensors are simultaneously activated. There is no continuous excitation voltage. In the exemplary embodiment of the invention, four sensors are used, consuming no more power than is required to operate one transducer continuously. It is particularly valuable to reduce power consumption if the data acquisition pod is intended for use in conjunction with a portable display such as display 20, with limited battery capacity.
  • the capacitor in sensor 302a is accessed by differential multiplexer 308.
  • the input signal to multiplexer 308 is differential.
  • the output signal 314 of multiplexer 308 is differential, except that one of the differential output lines of multiplexer 308 is tied to ground.
  • One electrode of the capacitor is tied to ground through multiplexer 308.
  • the capacitor output signal changes from a differential voltage to a single ended voltage.
  • the output signal 314 is thus a single ended voltage referenced to ground. This signal may be sensed by a single ended amplifier.
  • the output signals from networks 304b-304d are similarly converted to pressure difference signals.
  • the converter 308 is controlled by signals 309a-309f sent over a timing bus 368.
  • the timing bus 368 also controls the transducers, so that the converter acts as a time division multiplexer, transmitting signals representative of the respective transducers in round robin fashion.
  • the output signal 314 is multiplexed together with reference pressure signals 316a, 316b in multiplexer 312.
  • Multiplexer 312 is controlled by signals 313a-313c which are received from the timing bus 368.
  • the signal 317 is boosted by amplifier 318 so that it occupies a range of values coextensive with the input range of the A/D converter 320, which converts it to digital form.
  • the digital output data signal 322 is Manchester encoded in a logic gate array 324 and is sent out to the display 20 by data transmitter 332.
  • An EEPROM 326 is provided for local storage of calibration coefficients and/or alarm limits which may be used by gate array 324.
  • a data receiver 334 receives commands from the display 20.
  • a second EEPROM 372 stores permanent data, such as the serial number or revision level of a printed circuit board.
  • the output signals 351a and 351b from respective temperature sensors, 350a and 350b, are filtered and clamped by circuits 352a and 352b, to remove noise and to limit the signal range.
  • the filtered signals are provided to multiplexer 356, which produces a single TDM signal 357.
  • An offset signal 360 is added to the TDM signal 357 in adder 358, and the resulting signal is boosted in amplitude by amplifier 362.
  • the amplified signal 363 is multiplexed together with plus and minus five volt monitor signals provided by the step down power supply 310 in multiplexer 364.
  • the power supply monitor signals are provided to allow deviations from the nominal five volt operational power signal provided by power supply 310 to be detected.
  • the multiplexer output signal is then boosted by amplifier 366 and the resulting signal is provide to A/D converter 320.
  • the temperature data is provided to the logic gate array 324 where it is Manchester encoded and transmitted to the display.

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Abstract

Ensemble fonctionnel autonome d'acquisition de données (10) collectant une série de données analogiques représentant des signaux d'électrocardiogramme (ECG), la saturation du sang en oxygène et soit la température soit le débit cardiaque. Des données représentant des signaux d'électroencéphalogramme (EEG), la pression sanguine et la pression partielle du dioxyde de carbone sanguin peuvent également être recueillies. Cet ensemble fonctionnel d'acquisition de données (10) comprend des lignes (16) de réception de signaux analogiques de données provenant d'une série de capteurs (410). Les signaux analogiques sont filtrés et amplifiés (418), après quoi un multiplexeur (414) combine ces signaux analogiques. Le signal analogique combiné est converti (412) en un signal numérique. L'ensemble fonctionnel d'acquisition de données (10) peut être raccordé sélectivement à un affichage sur écran (20) pour apporter à cet affichage (20) les signaux de sortie multiplexés. Le cheminement des signaux (16) entre l'ensemble fonctionnel (10) et le patient est sensiblement plus court que le cheminement des signaux (18) entre l'ensemble fonctionnel (10) et le système d'affichage (20), afin de réduire les interférences HF sur les signaux analogiques.
PCT/US1993/011710 1992-12-11 1993-12-02 Ensemble fonctionnel d'acquisition de donnees pour systeme de surveillance de patient WO1994013197A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
JP6514250A JPH08504344A (ja) 1992-12-11 1993-12-02 患者モニタ装置のためのデータ収録ポッド装置
EP94905331A EP0673224A1 (fr) 1992-12-11 1993-12-02 Ensemble fonctionnel d'acquisition de donnees pour systeme de surveillance de patient

Applications Claiming Priority (2)

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US98941492A 1992-12-11 1992-12-11
US07/989,414 1992-12-11

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WO1994013197A1 true WO1994013197A1 (fr) 1994-06-23

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Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0850594A1 (fr) * 1996-12-02 1998-07-01 Medex, Incorporated Système de câbles pour équipement médical
WO1999034224A1 (fr) * 1997-12-23 1999-07-08 Telstra R & D Management Pty. Ltd. Systeme de surveillance de parametres electriques
EP1216651A1 (fr) * 2000-12-21 2002-06-26 BrainLAB AG Système médical sans fil d'acquisition et de traitement
EP1266605A2 (fr) * 2001-06-13 2002-12-18 REHAU AG + Co Adapteur integré pour connecter des capteurs neurochirurgicaux
WO2002085200A3 (fr) * 2001-04-23 2003-01-09 Cardionet Inc Selection adaptative d'une limite d'alarme dans la surveillance d'un patient
WO2008005812A2 (fr) * 2006-06-30 2008-01-10 Intel Corporation Procédé et appareil d'amplification de signaux multiples au moyen d'un canal amplificateur multiplexé unique avec réponse ca commandée par logiciel
WO2008014459A2 (fr) 2006-07-28 2008-01-31 Medtronic, Inc. Circuit de détection à multicomplexeur priorisé
CN102908151A (zh) * 2012-11-05 2013-02-06 北京超思电子技术股份有限公司 可测体温的血氧测量仪
US9474445B2 (en) 2001-04-23 2016-10-25 Braemar Manufacturing, Llc Controlling access to medical monitoring system

Families Citing this family (3)

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DE60000012T2 (de) * 2000-01-15 2002-05-29 Agilent Technologies Inc Fernmessungsystem mit Bestimmung der Positionsanweisung des Senders
KR20060040500A (ko) * 2004-11-06 2006-05-10 삼성전자주식회사 생체신호 측정 장치 및 방법
CN103169457A (zh) * 2011-12-23 2013-06-26 上海理工大学 多功能生理监护装置

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FR2145020A5 (fr) * 1971-07-06 1973-02-16 Richalet Jacques
US3910257A (en) * 1973-04-25 1975-10-07 Nasa Medical subject monitoring systems
US4686998A (en) * 1985-11-12 1987-08-18 Mediscan Research Limited Patient temperature and heartbeat rate monitoring system
WO1989000024A1 (fr) * 1987-06-30 1989-01-12 Micromedical Industries Pty Limited Moniteur physiologique modulaire

Patent Citations (4)

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FR2145020A5 (fr) * 1971-07-06 1973-02-16 Richalet Jacques
US3910257A (en) * 1973-04-25 1975-10-07 Nasa Medical subject monitoring systems
US4686998A (en) * 1985-11-12 1987-08-18 Mediscan Research Limited Patient temperature and heartbeat rate monitoring system
WO1989000024A1 (fr) * 1987-06-30 1989-01-12 Micromedical Industries Pty Limited Moniteur physiologique modulaire

Cited By (21)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0850594A1 (fr) * 1996-12-02 1998-07-01 Medex, Incorporated Système de câbles pour équipement médical
US5937950A (en) * 1996-12-02 1999-08-17 Medex, Inc. Cable system for medical equipment
WO1999034224A1 (fr) * 1997-12-23 1999-07-08 Telstra R & D Management Pty. Ltd. Systeme de surveillance de parametres electriques
EP1055130A1 (fr) * 1997-12-23 2000-11-29 Telstra R & D Management Pty. Ltd. Systeme de surveillance de parametres electriques
EP1055130A4 (fr) * 1997-12-23 2001-05-16 Telstra R & D Man Pty Ltd Systeme de surveillance de parametres electriques
US7294106B2 (en) 2000-12-21 2007-11-13 Brainlab Ag Cable-free medical detection and treatment system
US6782285B2 (en) 2000-12-21 2004-08-24 Brainlab Ag Cable-free medical detection and treatment system
EP1216651A1 (fr) * 2000-12-21 2002-06-26 BrainLAB AG Système médical sans fil d'acquisition et de traitement
WO2002085200A3 (fr) * 2001-04-23 2003-01-09 Cardionet Inc Selection adaptative d'une limite d'alarme dans la surveillance d'un patient
US9474445B2 (en) 2001-04-23 2016-10-25 Braemar Manufacturing, Llc Controlling access to medical monitoring system
EP2298158A1 (fr) * 2001-04-23 2011-03-23 Cardionet, Inc. Sélection adaptative d'une limite d'alarme dans la surveillance d'un patient
EP1266605A3 (fr) * 2001-06-13 2003-01-08 REHAU AG + Co Adapteur integré pour connecter des capteurs neurochirurgicaux
EP1266605A2 (fr) * 2001-06-13 2002-12-18 REHAU AG + Co Adapteur integré pour connecter des capteurs neurochirurgicaux
US8200317B2 (en) 2006-06-30 2012-06-12 Intel Corporation Method and apparatus for amplifying multiple signals using a single multiplexed amplifier channel with software controlled AC response
WO2008005812A2 (fr) * 2006-06-30 2008-01-10 Intel Corporation Procédé et appareil d'amplification de signaux multiples au moyen d'un canal amplificateur multiplexé unique avec réponse ca commandée par logiciel
WO2008005812A3 (fr) * 2006-06-30 2008-02-21 Intel Corp Procédé et appareil d'amplification de signaux multiples au moyen d'un canal amplificateur multiplexé unique avec réponse ca commandée par logiciel
TWI456932B (zh) * 2006-06-30 2014-10-11 Intel Corp 利用具有軟體控制交流響應之單一多工放大器通道來放大多重信號之方法與裝置
WO2008014459A2 (fr) 2006-07-28 2008-01-31 Medtronic, Inc. Circuit de détection à multicomplexeur priorisé
US7738951B2 (en) 2006-07-28 2010-06-15 Medtronic, Inc. Prioritized multicomplexor sensing circuit
WO2008014459A3 (fr) * 2006-07-28 2008-05-02 Medtronic Inc Circuit de détection à multicomplexeur priorisé
CN102908151A (zh) * 2012-11-05 2013-02-06 北京超思电子技术股份有限公司 可测体温的血氧测量仪

Also Published As

Publication number Publication date
JPH08504344A (ja) 1996-05-14
EP0673224A1 (fr) 1995-09-27

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