US20060217605A1 - Oximeter sensor with digital memory encoding sensor data - Google Patents
Oximeter sensor with digital memory encoding sensor data Download PDFInfo
- Publication number
- US20060217605A1 US20060217605A1 US11/444,788 US44478806A US2006217605A1 US 20060217605 A1 US20060217605 A1 US 20060217605A1 US 44478806 A US44478806 A US 44478806A US 2006217605 A1 US2006217605 A1 US 2006217605A1
- Authority
- US
- United States
- Prior art keywords
- sensor
- oximeter
- memory
- light
- identification data
- Prior art date
- Legal status (The legal status 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 status listed.)
- Abandoned
Links
Images
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01D—MEASURING NOT SPECIALLY ADAPTED FOR A SPECIFIC VARIABLE; ARRANGEMENTS FOR MEASURING TWO OR MORE VARIABLES NOT COVERED IN A SINGLE OTHER SUBCLASS; TARIFF METERING APPARATUS; MEASURING OR TESTING NOT OTHERWISE PROVIDED FOR
- G01D18/00—Testing or calibrating apparatus or arrangements provided for in groups G01D1/00 - G01D15/00
-
- 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
- A61B5/1455—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 using optical sensors, e.g. spectral photometrical oximeters
- A61B5/14551—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 using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
- A61B5/14552—Details of sensors specially adapted therefor
-
- 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
- A61B5/1495—Calibrating or testing of in-vivo probes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/08—Sensors provided with means for identification, e.g. barcodes or memory chips
- A61B2562/085—Sensors provided with means for identification, e.g. barcodes or memory chips combined with means for recording calibration data
Definitions
- the present invention relates to oximetry sensors and, in particular, pulse oximetry sensors which include coded information relating to characteristics of the sensor.
- Pulse oximetry is typically used to measure various blood flow characteristics including, but not limited to, the blood-oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the tissue, and the rate of blood pulsations corresponding to each heartbeat of a patient. Measurement of these characteristics has been accomplished by use of a non-invasive sensor which passes light through a portion of the patient's tissue where blood perfuses the tissue, and photoelectrically senses the absorption of light in such tissue. The amount of light absorbed is then used to calculate the amount of blood constituent being measured.
- the light passed through the tissue is selected to be of one or more wavelengths that are absorbed by the blood in an amount representative of the amount of the blood constituent present in the blood.
- the amount of transmitted light passed through the tissue will vary in accordance with the changing amount of blood constituent in the tissue and the related light absorption.
- such sensors have been provided with light sources and photodetectors that are adapted to operate at two different wavelengths, in accordance with known techniques for measuring blood oxygen saturation.
- Nellcor U.S. Pat. No. 5,645,059 the disclosure of which is hereby incorporated herein by reference, teaches coding information in sensor memory used to provide pulse modulated signal, to indicate the type of sensor (finger, nose), the wavelength of a second LED, the number of LEDs, the numerical correction terms to the standard curves, and an identifier of the manufacturer.
- FIG. 1 is a block diagram of a pulse oximeter system in accordance with an exemplary embodiment of the present invention.
- the present techniques provide a memory chip for use in an oximeter sensor, or an associated adapter or connector circuit.
- the memory chip allows the storing of different data to provide enhanced capabilities for the oximeter sensor.
- the techniques include unique uses of data stored in such a memory.
- the data stored in the memory chip includes information relating to use of the oximeter sensor.
- the memory chip may encode a sensor model identification that can be displayed on a display screen when the sensor is connected to an oximeter monitor.
- the memory may also encode a range of operating parameters such as light levels over which the sensor can function or a maximum drive current. The operating parameters are read by a controller circuit which uses the data read from the memory chip to control the functioning of the pulse oximetry system.
- FIG. 1 is a block diagram of a pulse oximeter system incorporating a calibration memory element 56 according to the invention.
- memory element 56 is a two-lead semiconductor digital memory chip.
- the calibration element is part of the sensor 50 which also includes red and infrared LEDs 52 as in the prior art, along with a detector 54 . If desired, LEDs 52 may be replaced with other light emitting elements such as lasers.
- the oximeter includes read circuit 60 , drive circuit 66 , look-up tables 62 and 63 , controller 64 , amplifier 72 , filter 74 , and analog-to-digital converter 76 .
- Read circuit 60 is provided for reading multiple coded values across the two leads 51 , 53 connected to calibration element 56 .
- One value is provided to a look-up table 62 to determine appropriate wavelength dependent coefficients for the oxygen saturation calculation, as in the prior art.
- the other value(s) are then provided to another look up table(s) 63 which provides input (e.g., coefficients) to other calculations performed by controller 64 . These additional calculations may enhance the performance and/or safety of the system.
- Controller 64 provides signals to a drive circuit 66 , to control the amount of drive current provided to LEDs 52 .
- detector 54 is connected through an amplifier 72 and a filter 74 to an A/D converter 76 .
- the signal must be within the analog range of the circuits employed.
- the signal should also be well within the range of AID converter 76 (e.g., one rule that may be applied is to adjust LED drives and amplifier gains so that both red and IR signals fall between 40 % and 80 % of full scale reading of converter 76 ).
- This utilizes correct and independent settings for both the red and infrared LEDs.
- the current techniques allow for another feedback path which may alter the LED settings based on other sensor characteristics contained in the coding of the calibration element 56 , which is discussed in further detail below.
- Memory 56 may, for example, be implemented as a random access memory (RAM), a FLASH memory, a programmable read only memory (PROM), an electrically erasable PROM, a similar programmable and/or erasable memory, any kind of erasable memory, a write once memory, or other memory technologies capable of write operations.
- RAM random access memory
- FLASH memory FLASH memory
- PROM programmable read only memory
- PROM electrically erasable PROM
- a similar programmable and/or erasable memory any kind of erasable memory
- write once memory or other memory technologies capable of write operations.
- Various types of data useful to a pulse oximetry system can be stored in memory 56 .
- data indicating a sensor model identification code corresponding to a particular sensor model can be encoded in memory 56 .
- an action can be encoded into memory element 56 indicating an action to be performing by the oximeter monitor in response to reading the sensor model identification code.
- an identification code in the form of text indicating the specific model of sensor can be digitally encoded into memory 56 and read by the oximeter monitor when the sensor is connected to the oximeter.
- An action indicating that the sensor model text is to be displayed by the oximeter monitor on a display screen can also be encoded in memory 56 .
- the identification code can be displayed in human readable form on a display screen connected to the pulse oximeter monitor.
- the identification code allows the oximeter instrument to display a text string indicating what sensor model is being used, e.g. “Nellcor OXISENSOR I1 D-25,” “Adult Digit Sensor,” or “Agilent N-25.”
- display text for a plurality of specific models of pulse oximeter sensors can be stored in a lookup table coupled in parallel with lookup tables 62 and 63 in the pulse oximeter monitor.
- the pulse oximeter monitor reads a sensor code from memory 56 when the sensor 50 is connected to the oximeter.
- the sensor identification code stored in memory 56 is used to locate display text stored in a lookup table that corresponds to a specific sensor model.
- the oximeter can display the display text for the specific sensor model on a display screen for viewing.
- the present techniques may eliminate the printing of a model name and number on the sensor itself. Even when model names and numbers are printed on a sensor, the text may become illegible after several uses. Displaying text that corresponds to a specific sensor model can be highly useful for users of pulse oximetry sensors. For example, it may be important to identify a sensor model so that instructions relating to a particular sensor model in the manufacturer's handbook can be identified. In addition, it may be desirable to identify a sensor model name or identification number when corresponding with the manufacturer.
- Digitally encoded data indicating a sensor model type in memory 56 or in a lookup table may be used to determine whether a sensor model is compatible with a particular pulse oximeter monitor.
- memory 56 may contain a code indicating a sensor model type that is read by controller 64 .
- Memory 56 can also encode an action indicating that controller 64 is to compare the code from memory 56 with a list of codes in a lookup table (or other oximeter monitor memory device) to determine if the sensor is compatible. If controller 64 successfully matches the code read from the sensor, the display text indicating the sensor model type is displayed on the display screen. If controller 64 does not recognize the code, an error message may be displayed on the display screen indicating that the oximeter monitor does not recognize the sensor, and the oximeter may refuse to operate until the sensor is replaced.
- a code can be stored in the sensor memory 56 identifying the sensor manufacturer.
- An action indicating a use for the code by the oximeter can also be stored in memory 56 .
- the code is read by controller 64 and is used for the purpose indicated by the action.
- the action may, for example, indicate that the code in memory 56 is to be used to indicate operability with oximeter monitors of other manufacturers.
- Controller 64 can recognize certain codes as indicating compatible oximeter sensors. If the oximeter monitor does not recognize the code, then controller 64 can display an error message on a display screen indicating that the sensor is not compatible, and/or controller 64 can shut down circuitry in the oximeter monitor that senses signals from the sensor until the sensor is replaced with a compatible sensor.
- Other information may also be encoded into memory 56 , read by the 17 monitor, and displayed for user reference.
- language codes or country codes can be stored in memory 56 , read, and displayed to the user. The user can select a language or country code so that messages are displayed, such as error messages, in the selected language or a language corresponding to the selected country.
- Messages may also be encoded into memory 56 .
- safety messages relating to the proper use of the sensor can be encoded in memory 56 and displayed on a display screen in human readable form.
- oximeter sensors are typically much less expensive to replace than oximeter monitor instruments, it is desirable to encode data corresponding to the updated algorithms in the sensors rather than in the oximeter monitors.
- One method for performing these updates is by encoding revisions to the algorithms used for calculating the patient parameters in memory within the oximeter monitor, while encoding updated software code or tuning coefficients in sensor memory 56 .
- the updated code or coefficients correspond to updated algorithms that are read by the oximeter monitor so that the updated algorithms can be applied to the standard algorithms preprogrammed into the oximeter. For example, a line of software code in an algorithm used by the oximeter monitor can be replaced by a updated line of code stored in memory 56 .
- Controller 64 can read the updated code or coefficients from memory 56 and apply the updated algorithms to signals received from detector 54 to determine accurate blood oxygen saturation levels, pulse rates, pulse amplitudes, perfusion data, blood pressure, and other patient data.
- the updated algorithms can also be used to allow only supported features to be used.
- the new code or coefficients become permanently stored in the oximeter monitor, along with a new algorithm revision number, and are utilized for all future sensor use until later updated.
- Encoding a sensor model identification code could also be used to accommodate sensor-specific operating parameters such as LED drive currents or “sensor off” characteristics (as an alternative to programming the value of drive current or “off” characteristics themselves).
- sensor-specific operating parameters such as LED drive currents or “sensor off” characteristics (as an alternative to programming the value of drive current or “off” characteristics themselves).
- photosignals coming from the sensor LEDs generally fall within a certain range.
- the photosignal usually changes. This is particularly true for the reusable clip-style sensor, because in their normal disconnected state, the LEDs shine directly onto the photodetector unimpeded by, for example, tissue.
- a “threshold photocurrent” into memory chip 56 reliable detection of a “sensor is off the patient” condition can be accomplished. In this example, exceeding a certain detected threshold light level is an indication that the sensor is not on a finger or other site.
- a low light level may be indicative of the sensor being off.
- An adhesive sensor for example, lays flat when in it's natural state—little LED light may reach the detector. Encoding an expected range of light levels for the specific model of sensor being used into memory 56 allows enhanced detection of when the sensor is improperly placed or has been removed.
- the oximeter monitor can display an “sensor off” message on a display screen indicating to the medical personnel that the sensor is not in an operable position and that valid data cannot be detected (i.e., a sensor off condition).
- the oximeter monitor can also emit an alarm signal until the light level detected by photodetector 54 reaches the expected range.
- expected ranges of light levels (or other parameters such as pulse size) that are specific to a particular patient may be encoded and saved into memory 56 by the clinical through the oximeter.
- the oximeter compares the expected range for the parameters encoded into memory 56 with data received from the photodetector to determine a sensor off condition each time the sensor is used until the range data is overwritten with new data. This is advantageous because light levels, pulse sizes, and other parameters detected by the photodetector can vary significantly from patient to patient.
- Existing pulse oximeter sensors determine whether a sensor is off the patient, or not in good contact by using a number of metrics.
- Those metrics include pulse size, pulse variability, IR/Red correlation, light level variability, pulse shape, and pulse regularity. Not only the light level, but any of these other values could vary depending on the type of sensor, the characteristics of an individual patient, and the location on the body where the sensor is to be applied.
- sensor memory 56 could encode information about the expected variation in any of these metrics for the particular sensor type or model or a particular patient, and these metrics may be used in determining if a sensor is off from any combination of these or other metrics as an indication that the sensor is off the patient.
- pulses could be typically weaker on the forehead compared to the finger.
- Memory device 56 of an oximeter sensor designed for use on the forehead of a patient can be encoded with a range of pulse sizes as well as a range of light levels that are expected from that particular oximeter sensor model. If desired, memory 56 can encode a range of numbers based upon light level and pulse size (and other parameters). For example, memory 56 can encode a range of numbers representing the expected range of pulse size times light level received from detector 54 for a specific sensor model.
- Controller 64 reads and decodes the pulse size, light level range, and other data encoded in memory 56 . Controller 64 then compares the expected pulse size and light level range data with the information received from detector 54 . When the pulse size and/or light level data received from detector 54 exceeds or falls below the expected range data encoded in memory 56 , the oximeter monitor displays an output message, e.g., a warning of a poor signal, on the display screen indicating that the sensor is not operable or emits an alarm signal. Further details of a Method and Circuit for Indicating Quality and Accuracy of Physiological Measurements are discussed in U.S.
- Running LEDs 52 at a high drive current results in more light output from the LEDs, thus improving the signal-to-noise ratio of the blood oxygen saturation signal from detector 54 , but comes at a cost of causing additional heat dissipation (i.e., the LEDs run “hotter”).
- the majority of the energy output by the LEDs is dissipated as heat, and the smaller portion of the energy output by the LEDs is emitted as light. This heat typically causes the temperature of the skin under the sensor to rise by an amount that that depends on the heat dissipation properties of the sensor.
- the oximeter instrument can utilize the highest safe drive current for the sensor being used to attain the greatest amount of LED light without risk of injury.
- the maximum safe drive current allowed to achieve a skin temperature at or below a maximum level can be determined in advance through testing for a given oximeter sensor model. That maximum drive current can be encoded into memory 56 and read by controller 64 when the sensor is connected to the oximeter monitor. Controller 64 then communicates with drive circuit 66 to drive LEDs 52 at or near the maximum drive current value read from memory 56 , but to prevent circuit 66 from driving LEDs 52 with a current that exceeds the maximum drive current.
- Encoded text of the specific model of sensor would allow the instrument to display a text string indicating what sensor is being used, e.g. “Nellcor OXISENSOR II D-25” or “Adult Digit Sensor” or “Agilent N-25”.
- a sensor code could be stored that points to a lookup table of display text.
- Encoding sensor model ID could also be used to accommodate sensor-specific operating parameters such as LED drive currents or “sensor off” characteristics (as an alternative to programming the value of drive current or “off” characteristics themselves).
- the sensor may store a general polynomial curve. Other families of polynomials, such as Tchebyschev polynomials, could be used as well. This may also pertain to other calibration information, such as temperature calibration and force transducer calibration. This allows new sensor types (such as a sensor with an offset emitter and detector).
- a low light level may be indicative of the sensor being off (an adhesive sensor, for example, lays flat when in its natural state, so little LED light may reach the detector). Encoding an expected range of light levels for the specific model of sensor being used allows enhanced detection of when the sensor is improperly placed or has been removed.
- the STORM algorithm here refers to the sensors designed to be used where “motion provides the signal”, i.e., the cardiac pulse need not be present or discernible in order for the oximeter to provide SpO 2 values. Instead, the red and IR waveforms resulting from the motion itself are used for determining the arterial saturation. This feature is possible for tissue beds that are well “arterialized” (a large supply of arterial blood relative to the metabolic needs of the tissue) resulting in a small aterio-venous saturation difference, as well as other signal characteristics that are not germane to this discussion. It has been observed that the necessary degree of arterialization correlates well to being “well perfused” at the tissue site, which itself correlates well to the tissue bed being warm. Thus by monitoring the temperature of the skin at the sensor site, and by knowing a value of temperature (programmed into the memory chip) at which the “motion-is-signal” algorithm can be utilized for the specific sensor design being used, improved reading accuracy through motion can be better accomplished.
- an extrinsic probe of skin contact can be used to indicate whether the sensor is in adequate contact to the patient.
- This extrinsic probe could be accomplished, for example, through an impedance measurement across two electrodes, a force or pressure switch that is sensitive to whether adequate force or pressure is present in the sensor placement, or through other means.
- Dedicated sensor connector pins, or pin-sharing, could be used to accomplish this additional measure of sensor-patient contact.
- An electrochemical or thermal device that senses and stores to memory the number of exposures (zero, once, or potentially more than once or the actual number) to sterilization cycles could be used to capture the history of the sensor. Excessive exposure to sterilization cycles degrades a number of components in the sensor, and can affect its performance. A sensor exceeding a certain number of exposures could cause a display to indicate the sensor needs to be replaced.
- the expiration date of the sensor may be written into the memory chip.
- the memory-enabled instrument would then do something with this knowledge (e.g., indicate “expired sensor”, or refuse to function if expired).
- the elapsed time of sensor usage could be tracked in the memory chip (written to it by the instrument) and the sensor would “expire” after a memory programmed maximum (greater for reusable sensors than for single-use sensors).
- the instrument may refuse to function with this sensor and would indicate that a fresh sensor is needed. Furthermore, the sensor could be disabled by running a high current through it, or by other means.
- the date of expiration of the sensor warranty could be written into the memory chip (e.g., 2, or 6, or 12, etc. months from the date of 10 manufacture or the date of first use). The instrument would give some indication of this as appropriate.
- Trending and/or data logging of patient monitoring parameters may be stored in the memory of the memory chip. As the patient and sensor travel from ward-to-ward of the hospital., and consequently plug into different oximeters, the patient-specific data could be displayed as it is contained in the patient's dedicated sensor. Examples of the type of data are given below:
- the lowest and/or highest SpO 2 value during the monitored time, or the lowest/highest values over the past specified monitoring time e.g., 2 hours, 1 day, etc.
- the alarm limits used with this patient become written to the memory chip by the instrument. This allows patient-specific alarm values to be set and memorized so that as the patient moves from monitor-to monitor (the sensor staying with the patient), the appropriate alarm limits need not be reset each time on the new monitor. Instead, this only needs to happen once, or whenever the clinician adjusts alarm limits.
- Data encryption utilizes private and/or public keys to scramble the data written to the memory chip and later decipher the data so that only authorized devices are supported.
- the sensor manufacturing system could periodically change the private and/or public keys. The change in the key could be communicated to the instrument via the memory chip in encrypted form. The purpose of this feature is to elevate the level of security in the memory system.
- LED and detector parameters in the sensor memory Another reason for recording LED and detector parameters in the sensor memory is to provide a basis for later research on the drift of these parameters due to various environmental conditions which the sensor experiences.
- Parameters of interest include not only LED power and detector sensitivity, but also LED wavelengths, FWHM, and secondary emission level.
- the accuracy of the sensor may be different for patients with different skin color.
- the sensitivity of accuracy to skin color may depend on sensor model.
- the sensor might contain a sensitivity index, indicating how large an adjustment in readings should be made as a function of skin color. Skin color might be obtained by user entry of the data (e.g. menu selection).
- Another option would be for the sensor to measure skin color.
- One way to achieve the latter option would be to provide transmission sensors with auxiliary detector for “reflected” light. In combination with the optical efficiency information noted above, the signal levels reported by the auxiliary detector would sense to what extent the patient's skin was affecting red and IR pathlengths differently, and hence to what extent readings needed to be corrected.
- Accelerometer data may be used to warn of the presence of motion (in which case special algorithms may be called into play or oximetry may be suspended), or actually to help correct for motion (to the extent to which we can produce algorithms which can predict physio-optic effects of known motion).
- the amount of optical shunting could be measured for each sensor, or family of sensors.
- the value would be stored in the sensory memory for the monitor to read and use to adjust the processing coefficients.
- the temperature of a red LED affects its principal wavelength, which affects calibration. For one class of LEDs, the wavelength shifts by about 0.14 nm/C.
- the memory chip might contain circuitry capable of monitoring a thermistor or thermocouple, or the memory chip could be mounted in proximity to the LED (e.g. under it), so that it could sense directly the temperature of the LED, and provide a calibration correction accordingly.
- thermometric sensor a passive component on the memory chip
- a resistance or voltage measuring device in the instrument could read out that sensor.
- ambient temperature sensing might not require that large changes be made in the memory chip.
- the temperature amplifier/detector would allow the LEDs to be driven to a level that still results in a safe temperature by monitoring the temperature, yet in many cases allow more drive current, and therefore higher signals, which could give better readings.
- the inexpensive thermistor devices that could be used in this application are characterized to allow the measurement to be accurate. These characterization values could be stored in the sensor where the thermistor is located. While in operation, the oximeter would be able to read the characterization values from the sensor, measure the resistance of the thermistor, and calculate accurately the temperature of the skin surface where the thermistor is located. This would keep the patient safe from bums and still provide the best signal available.
- memory compatible oximeters When adding the memory chip, memory compatible oximeters will be able to obtain the necessary calibration coefficients from the memory chip but the legacy instruments will still need a calibration resistor value. If the resistance were built-in to the chip and trimmed or selected at manufacture then only one device would need to be installed in the sensor connector. That would reduce the overall cost, yet keep the sensor compatible with both the legacy instruments and the new memory compatible instruments.
- the oximeter is measuring the relative transmission of the red and infrared light through the tissue.
- LEDs have a characteristic called secondary emission which is indicative of the amount of light, at wavelengths other than the primary wavelength, that is being emitted. This characteristic will change the calibration of the device if not compensated for. It is possible to make an oximeter that will function within calibration if the secondary emission is known and compensated for. If the LED were characterized during manufacture and then the secondary emission values entered into the memory chip, the oximeter would be able to read those values and compensate for them so that the sensor was used properly. This would increase the range of LEDs that could be used for oximetry, reduce cost and provide better calibration across a wider range of LED emitters.
- Patient ID (Potentially as Tracking Device, Archiving Patient History, etc.)
- one of the factors that can influence that measurement is the contact resistance of the connectors that are between the oximeter and the resistor itself.
- One of the interfering noise sources that plagues oximetry is that of common mode noise. This can come from the surrounding electrical environment. Other instruments, lighters, drills etc. can produce electrical fields that can couple into the cable between the patient and the oximeter. Once coupled-in, they can make measurements more difficult, less accurate, or not possible, depending on the severity of the noise.
- differential amplifiers are used for amplifying the signal from the sensor. These amplifiers amplify only the difference between two signal wires. Thus, if the common mode signal is coupled exactly the same into both wires, the amplifier will not amplify it because the same signal is present on both wires.
- the two wires have different coupling to their electrical environment, then they will present different signals, and the difference will be amplified as if it were a signal.
- One component that influences this coupling is the capacitance of the lines to the outside world. This is affected by the manufacture of the cable, materials, twists in the wire, etc. If one measured the cables during manufacture and then stored that information in the memory chip, it could be read when the oximeter is operating. Once the capacitances for the two wires to the shield are known, the instrument could be provided with a tunable capacitance device that would then balance the two lines again and make the noise coupling to the lines better matched. This would reduce the amount of susceptibility to the external noise that got coupled into the patient cable. Reduced noise results in better measurements or the ability to make measurements at all on some patients.
- the relative wavelengths of the red and infrared light that is used to make the measurement in oximetry are important to know so that calibration can be maintained.
- the LED sources are at the skin so that whatever wavelength is emitted is what is sensed by the photodiode that receives the light.
- the red LED is the only one that we need to characterize for accurate saturation measurements to be realized. The saturation is less sensitive to the IR wavelength as long as it stays fixed in the acceptable range that has been specified for the IR LEDs.
- the accuracy of the oximetry measurement can also be improved by using different wavelengths at different saturation ranges.
- An analysis unit could be developed that would utilize either or both of these features. To do this, it would be able to drive additional LEDs. The additional LEDs could be driven along with the traditional ones or separately.
- the oximeter (or additional constituent measurement unit) would provide the capability to calculate values for these other wavelengths, and the sensor would provide the additional information to allow the oximeter to make that calculation. These could be stored in the memory.
- One of the problems with oximetry sensors is the interference caused by ambient light in the environment. This can be made worse when a sensor comes loose or when the ambient light is extremely high in value. By characterizing the sensor, one could know what level of ambient light could be expected or tolerated, and give a warning to the user when the level has been exceeded. This would give them the opportunity to adjust the sensor, the light, or both to affect an improvement in the performance of the oximeter.
- One way to enhance the modulation percentage is to apply pressure in the range of the median pulsatile pressure. If this were implemented, one could use relatively low cost transducers and supply calibration coefficients in the memory to allow accurate pressure readings to be made.
- the memory could also contain the pressure settings and/or expected modulation enhancement capability to determine effectiveness of the pressure enhancement.
- the amount of perfusion affects the amount of modulation, and thus the AC signal. This affects both the percentage of modulation vs. the DC amount, and the absolute size of the modulation.
- the measured modulation, or other measurement of perfusion can be stored in memory for trending or setting limits on acceptable perfusion before movement or other adjustment of the sensor is required.
- Disconnecting can be detected from the interruption of the signal to the monitor. Moving can be detected by a sensor off detection, and a subsequent sensor on detection. Alternately, aggressive movement could be detected and interpreted as moving of the sensor, or a combination with a sensor off detection could be used.
- a code can be stored in the sensor memory identifying the sensor manufacturer. This code can be read and used to indicate operability with monitors of other manufacturers, or to indicate any conversion algorithm that may be needed for a signal from a sensor to be used by a monitor from a different manufacturer. The code can also be used to allow only supported features to be used.
- a moisture sensor or impedance sensor can detect the amount of wetness of the sensor. This can be used for different purposes and can be stored in the sensor memory for trending or monitoring. To determine sensor malfunction, the sensor can be disabled if the wetness exceeds a threshold, which could be stored in the sensor memory. Some sensors may not provide for isolation of the patient from the electronics for excessive wetness. The maximum allowable wetness could be stored in the sensor memory.
- the sensor memory could identify that the sensor provides isolation, so wetness is not a concern. Alternately, it could indicate that isolation is not provided by the sensor, or a limited amount of isolation is provided.
- a portable battery-powered monitor can power down when the saturation is at a good level, and the patient is stable. Minimal circuitry in the sensor could be used to do sufficient processing to tell the monitor when to wake up.
- a battery can be included in the sensor for a wireless connection to a monitor. Alternately, a battery could be used to continue to send data when the monitor is powered down.
- the sensor can include a cuff (which inflates and deflates) or other mechanical mechanism for inducting motion to get a signal or for inducing pulsitile blood flow to improve the signal.
- a cuff which inflates and deflates
- other mechanical mechanism for inducting motion to get a signal or for inducing pulsitile blood flow to improve the signal.
- a transducer can measure the amount of force on the sensor. This can be compared to a maximum value stored in the sensor memory to determine if the sensor is on too tight. The tightness can also be recorded and monitored. For example, a patient could swell, and this could be determined from the trend information and provided as information to a clinician on a display.
- a calibration value can be stored in the sensor memory for converting a force measurement into a pressure measurement.
- a force transducer can then be used to measure pressure.
- the sensor memory can store an indication of the number of wavelengths used in the sensor, and could store the wavelengths themselves.
- the sensor memory can store information about when to drive which LEDs. They could all be driven at once, or a subset could be driven, for example.
- the memory can store information about what parameters are to be analyzed and displayed when the extra wavelengths are used. Oxygen saturation may be displayed when 2 wavelengths are used, while additional information could be displayed when an extra wavelength or more are used (Hct, COHb, etc.).
- a number in the sensor memory can be incremented. This can be used to prevent operation of the sensor if it has been recycled more than the allowed number of times (e.g., 3 times).
Landscapes
- Health & Medical Sciences (AREA)
- Physics & Mathematics (AREA)
- Life Sciences & Earth Sciences (AREA)
- Medical Informatics (AREA)
- Surgery (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Veterinary Medicine (AREA)
- Molecular Biology (AREA)
- Optics & Photonics (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Spectroscopy & Molecular Physics (AREA)
- General Physics & Mathematics (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
Abstract
Description
- This application is a continuation of U.S. patent application Ser. No. 10/440,560, filed May 16, 2003, which is a continuation application of U.S. patent application Ser. No. 09/943,805, filed Aug. 30, 2001, now U.S. Pat. No. 6,591,123, which claims the benefit of U.S. Provisional Application Ser. No. 60/299,616, filed Aug. 31, 2000, all of which are incorporated herein by reference.
- The present invention relates to oximetry sensors and, in particular, pulse oximetry sensors which include coded information relating to characteristics of the sensor.
- Pulse oximetry is typically used to measure various blood flow characteristics including, but not limited to, the blood-oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the tissue, and the rate of blood pulsations corresponding to each heartbeat of a patient. Measurement of these characteristics has been accomplished by use of a non-invasive sensor which passes light through a portion of the patient's tissue where blood perfuses the tissue, and photoelectrically senses the absorption of light in such tissue. The amount of light absorbed is then used to calculate the amount of blood constituent being measured.
- The light passed through the tissue is selected to be of one or more wavelengths that are absorbed by the blood in an amount representative of the amount of the blood constituent present in the blood. The amount of transmitted light passed through the tissue will vary in accordance with the changing amount of blood constituent in the tissue and the related light absorption. For measuring blood oxygen level, such sensors have been provided with light sources and photodetectors that are adapted to operate at two different wavelengths, in accordance with known techniques for measuring blood oxygen saturation.
- Nellcor U.S. Pat. No. 5,645,059, the disclosure of which is hereby incorporated herein by reference, teaches coding information in sensor memory used to provide pulse modulated signal, to indicate the type of sensor (finger, nose), the wavelength of a second LED, the number of LEDs, the numerical correction terms to the standard curves, and an identifier of the manufacturer.
-
FIG. 1 is a block diagram of a pulse oximeter system in accordance with an exemplary embodiment of the present invention. - The present techniques provide a memory chip for use in an oximeter sensor, or an associated adapter or connector circuit. The memory chip allows the storing of different data to provide enhanced capabilities for the oximeter sensor. In addition to providing unique data to store in such a memory, the techniques include unique uses of data stored in such a memory. The data stored in the memory chip includes information relating to use of the oximeter sensor. For example, the memory chip may encode a sensor model identification that can be displayed on a display screen when the sensor is connected to an oximeter monitor. The memory may also encode a range of operating parameters such as light levels over which the sensor can function or a maximum drive current. The operating parameters are read by a controller circuit which uses the data read from the memory chip to control the functioning of the pulse oximetry system.
-
FIG. 1 is a block diagram of a pulse oximeter system incorporating acalibration memory element 56 according to the invention. In one embodiment,memory element 56 is a two-lead semiconductor digital memory chip. The calibration element is part of thesensor 50 which also includes red andinfrared LEDs 52 as in the prior art, along with adetector 54. If desired,LEDs 52 may be replaced with other light emitting elements such as lasers. - The oximeter includes
read circuit 60,drive circuit 66, look-up tables 62 and 63,controller 64,amplifier 72,filter 74, and analog-to-digital converter 76. Readcircuit 60 is provided for reading multiple coded values across the two leads 51,53 connected tocalibration element 56. One value is provided to a look-up table 62 to determine appropriate wavelength dependent coefficients for the oxygen saturation calculation, as in the prior art. The other value(s) are then provided to another look up table(s) 63 which provides input (e.g., coefficients) to other calculations performed bycontroller 64. These additional calculations may enhance the performance and/or safety of the system.Controller 64 provides signals to adrive circuit 66, to control the amount of drive current provided toLEDs 52. - As in the prior art,
detector 54 is connected through anamplifier 72 and afilter 74 to an A/D converter 76. This forms a feedback path used bycontroller 64 to adjust the drive current to optimize the intensity range of the signal received. For proper operation the signal must be within the analog range of the circuits employed. The signal should also be well within the range of AID converter 76 (e.g., one rule that may be applied is to adjust LED drives and amplifier gains so that both red and IR signals fall between 40% and 80% of full scale reading of converter 76). This utilizes correct and independent settings for both the red and infrared LEDs. The current techniques allow for another feedback path which may alter the LED settings based on other sensor characteristics contained in the coding of thecalibration element 56, which is discussed in further detail below. -
Memory 56 may, for example, be implemented as a random access memory (RAM), a FLASH memory, a programmable read only memory (PROM), an electrically erasable PROM, a similar programmable and/or erasable memory, any kind of erasable memory, a write once memory, or other memory technologies capable of write operations. Various types of data useful to a pulse oximetry system can be stored inmemory 56. For example, data indicating a sensor model identification code corresponding to a particular sensor model can be encoded inmemory 56. Also, an action can be encoded intomemory element 56 indicating an action to be performing by the oximeter monitor in response to reading the sensor model identification code. - For example, an identification code in the form of text indicating the specific model of sensor can be digitally encoded into
memory 56 and read by the oximeter monitor when the sensor is connected to the oximeter. An action indicating that the sensor model text is to be displayed by the oximeter monitor on a display screen can also be encoded inmemory 56. The identification code can be displayed in human readable form on a display screen connected to the pulse oximeter monitor. The identification code allows the oximeter instrument to display a text string indicating what sensor model is being used, e.g. “Nellcor OXISENSOR I1 D-25,” “Adult Digit Sensor,” or “Agilent N-25.” - Alternately, display text for a plurality of specific models of pulse oximeter sensors can be stored in a lookup table coupled in parallel with lookup tables 62 and 63 in the pulse oximeter monitor. The pulse oximeter monitor reads a sensor code from
memory 56 when thesensor 50 is connected to the oximeter. The sensor identification code stored inmemory 56 is used to locate display text stored in a lookup table that corresponds to a specific sensor model. The oximeter can display the display text for the specific sensor model on a display screen for viewing. - The present techniques may eliminate the printing of a model name and number on the sensor itself. Even when model names and numbers are printed on a sensor, the text may become illegible after several uses. Displaying text that corresponds to a specific sensor model can be highly useful for users of pulse oximetry sensors. For example, it may be important to identify a sensor model so that instructions relating to a particular sensor model in the manufacturer's handbook can be identified. In addition, it may be desirable to identify a sensor model name or identification number when corresponding with the manufacturer.
- Digitally encoded data indicating a sensor model type in
memory 56 or in a lookup table may be used to determine whether a sensor model is compatible with a particular pulse oximeter monitor. For example,memory 56 may contain a code indicating a sensor model type that is read bycontroller 64.Memory 56 can also encode an action indicating thatcontroller 64 is to compare the code frommemory 56 with a list of codes in a lookup table (or other oximeter monitor memory device) to determine if the sensor is compatible. Ifcontroller 64 successfully matches the code read from the sensor, the display text indicating the sensor model type is displayed on the display screen. Ifcontroller 64 does not recognize the code, an error message may be displayed on the display screen indicating that the oximeter monitor does not recognize the sensor, and the oximeter may refuse to operate until the sensor is replaced. - A code can be stored in the
sensor memory 56 identifying the sensor manufacturer. An action indicating a use for the code by the oximeter can also be stored inmemory 56. The code is read bycontroller 64 and is used for the purpose indicated by the action. The action may, for example, indicate that the code inmemory 56 is to be used to indicate operability with oximeter monitors of other manufacturers.Controller 64 can recognize certain codes as indicating compatible oximeter sensors. If the oximeter monitor does not recognize the code, thencontroller 64 can display an error message on a display screen indicating that the sensor is not compatible, and/orcontroller 64 can shut down circuitry in the oximeter monitor that senses signals from the sensor until the sensor is replaced with a compatible sensor. - Other information may also be encoded into
memory 56, read by the 17 monitor, and displayed for user reference. For example, language codes or country codes can be stored inmemory 56, read, and displayed to the user. The user can select a language or country code so that messages are displayed, such as error messages, in the selected language or a language corresponding to the selected country. Messages may also be encoded intomemory 56. For example, safety messages relating to the proper use of the sensor can be encoded inmemory 56 and displayed on a display screen in human readable form. - It is often desirable to upgrade the algorithms that are used by the oximeter to determine blood oxygen saturation levels, pulse rates, pulse amplitude, blood pressure, and other patient data as technology progresses and the operating parameters (such as filter coefficients) are refined. Because oximeter sensors are typically much less expensive to replace than oximeter monitor instruments, it is desirable to encode data corresponding to the updated algorithms in the sensors rather than in the oximeter monitors.
- One method for performing these updates is by encoding revisions to the algorithms used for calculating the patient parameters in memory within the oximeter monitor, while encoding updated software code or tuning coefficients in
sensor memory 56. The updated code or coefficients correspond to updated algorithms that are read by the oximeter monitor so that the updated algorithms can be applied to the standard algorithms preprogrammed into the oximeter. For example, a line of software code in an algorithm used by the oximeter monitor can be replaced by a updated line of code stored inmemory 56. -
Controller 64 can read the updated code or coefficients frommemory 56 and apply the updated algorithms to signals received fromdetector 54 to determine accurate blood oxygen saturation levels, pulse rates, pulse amplitudes, perfusion data, blood pressure, and other patient data. The updated algorithms can also be used to allow only supported features to be used. In one embodiment, once updated, the new code or coefficients become permanently stored in the oximeter monitor, along with a new algorithm revision number, and are utilized for all future sensor use until later updated. - Encoding a sensor model identification code could also be used to accommodate sensor-specific operating parameters such as LED drive currents or “sensor off” characteristics (as an alternative to programming the value of drive current or “off” characteristics themselves). Under normal operating conditions, photosignals coming from the sensor LEDs generally fall within a certain range. When a sensor is removed from a patient, or falls off on it's own, the photosignal usually changes. This is particularly true for the reusable clip-style sensor, because in their normal disconnected state, the LEDs shine directly onto the photodetector unimpeded by, for example, tissue. By programming a “threshold photocurrent” into
memory chip 56, reliable detection of a “sensor is off the patient” condition can be accomplished. In this example, exceeding a certain detected threshold light level is an indication that the sensor is not on a finger or other site. - For certain other sensors, a low light level may be indicative of the sensor being off. An adhesive sensor, for example, lays flat when in it's natural state—little LED light may reach the detector. Encoding an expected range of light levels for the specific model of sensor being used into
memory 56 allows enhanced detection of when the sensor is improperly placed or has been removed. Whencontroller 64 senses that the light level output detected byphotodetector 54 has fallen below or exceeded the expected range of light levels encoded intomemory 56, the oximeter monitor can display an “sensor off” message on a display screen indicating to the medical personnel that the sensor is not in an operable position and that valid data cannot be detected (i.e., a sensor off condition). The oximeter monitor can also emit an alarm signal until the light level detected byphotodetector 54 reaches the expected range. - If desired, expected ranges of light levels (or other parameters such as pulse size) that are specific to a particular patient may be encoded and saved into
memory 56 by the clinical through the oximeter. The oximeter compares the expected range for the parameters encoded intomemory 56 with data received from the photodetector to determine a sensor off condition each time the sensor is used until the range data is overwritten with new data. This is advantageous because light levels, pulse sizes, and other parameters detected by the photodetector can vary significantly from patient to patient. - Existing pulse oximeter sensors determine whether a sensor is off the patient, or not in good contact by using a number of metrics. Those metrics include pulse size, pulse variability, IR/Red correlation, light level variability, pulse shape, and pulse regularity. Not only the light level, but any of these other values could vary depending on the type of sensor, the characteristics of an individual patient, and the location on the body where the sensor is to be applied. Thus,
sensor memory 56 could encode information about the expected variation in any of these metrics for the particular sensor type or model or a particular patient, and these metrics may be used in determining if a sensor is off from any combination of these or other metrics as an indication that the sensor is off the patient. - For example, pulses could be typically weaker on the forehead compared to the finger.
Memory device 56 of an oximeter sensor designed for use on the forehead of a patient can be encoded with a range of pulse sizes as well as a range of light levels that are expected from that particular oximeter sensor model. If desired,memory 56 can encode a range of numbers based upon light level and pulse size (and other parameters). For example,memory 56 can encode a range of numbers representing the expected range of pulse size times light level received fromdetector 54 for a specific sensor model. -
Controller 64 reads and decodes the pulse size, light level range, and other data encoded inmemory 56.Controller 64 then compares the expected pulse size and light level range data with the information received fromdetector 54. When the pulse size and/or light level data received fromdetector 54 exceeds or falls below the expected range data encoded inmemory 56, the oximeter monitor displays an output message, e.g., a warning of a poor signal, on the display screen indicating that the sensor is not operable or emits an alarm signal. Further details of a Method and Circuit for Indicating Quality and Accuracy of Physiological Measurements are discussed in U.S. patent application Ser. No. 09/545,170, filed Apr. 6, 2000 to Porges, et al., which is incorporated by reference herein in its entirety. - Running
LEDs 52 at a high drive current results in more light output from the LEDs, thus improving the signal-to-noise ratio of the blood oxygen saturation signal fromdetector 54, but comes at a cost of causing additional heat dissipation (i.e., the LEDs run “hotter”). As current flows through the sensor LEDs, the LED emits heat (i.e., the LED power=LED drive current times the voltage drop across the LED). The majority of the energy output by the LEDs is dissipated as heat, and the smaller portion of the energy output by the LEDs is emitted as light. This heat typically causes the temperature of the skin under the sensor to rise by an amount that that depends on the heat dissipation properties of the sensor. Current safety regulations and guidelines limit the temperature of the skin contacting portions of the sensor to remain at or below 41° C. Sensors that do a poor job of directing the heat away from the skin contacting surface, should use a lower LED drive current. Sensors with good thermal management can utilize higher drive currents without risk to the patient. - Accordingly, by encoding the maximum safe LED drive current into the sensor itself, the oximeter instrument can utilize the highest safe drive current for the sensor being used to attain the greatest amount of LED light without risk of injury. The maximum safe drive current allowed to achieve a skin temperature at or below a maximum level can be determined in advance through testing for a given oximeter sensor model. That maximum drive current can be encoded into
memory 56 and read bycontroller 64 when the sensor is connected to the oximeter monitor.Controller 64 then communicates withdrive circuit 66 to driveLEDs 52 at or near the maximum drive current value read frommemory 56, but to preventcircuit 66 from drivingLEDs 52 with a current that exceeds the maximum drive current. - Embodiments of the present technique include the following:
- Sensor Model ID
- Encoded text of the specific model of sensor would allow the instrument to display a text string indicating what sensor is being used, e.g. “Nellcor OXISENSOR II D-25” or “Adult Digit Sensor” or “Agilent N-25”. Alternately, a sensor code could be stored that points to a lookup table of display text. Encoding sensor model ID could also be used to accommodate sensor-specific operating parameters such as LED drive currents or “sensor off” characteristics (as an alternative to programming the value of drive current or “off” characteristics themselves).
- Sensor Model—Specific Information
- Coefficients for Taylor's Series Calibration Curves
- The sensor may store a general polynomial curve. Other families of polynomials, such as Tchebyschev polynomials, could be used as well. This may also pertain to other calibration information, such as temperature calibration and force transducer calibration. This allows new sensor types (such as a sensor with an offset emitter and detector).
- Sensor Adiustment/Re-Application Light Levels
- Sensor Off Light Levels
- Under normal operating conditions, photosignals coming from the sensor LEDs generally fall within a certain range. When a sensor is removed from a patient, or falls off on its own, the photosignal usually changes. This is particularly true for the reusable clip-style sensor, since in their normal disconnected state, the LEDs shine directly onto the photodetector unimpeded by, for example, tissue. By programming a “threshold photocurrent” into the memory chip, reliable detection of a “sensor is off the patient” condition can be accomplished (in this example, exceeding a certain detected light level is a sure sign the sensor is not on a finger or other opposed site). For certain other sensors, a low light level may be indicative of the sensor being off (an adhesive sensor, for example, lays flat when in its natural state, so little LED light may reach the detector). Encoding an expected range of light levels for the specific model of sensor being used allows enhanced detection of when the sensor is improperly placed or has been removed.
- Temperature at Which to Switch to STORM Algorithm
- The STORM algorithm here refers to the sensors designed to be used where “motion provides the signal”, i.e., the cardiac pulse need not be present or discernible in order for the oximeter to provide SpO2 values. Instead, the red and IR waveforms resulting from the motion itself are used for determining the arterial saturation. This feature is possible for tissue beds that are well “arterialized” (a large supply of arterial blood relative to the metabolic needs of the tissue) resulting in a small aterio-venous saturation difference, as well as other signal characteristics that are not germane to this discussion. It has been observed that the necessary degree of arterialization correlates well to being “well perfused” at the tissue site, which itself correlates well to the tissue bed being warm. Thus by monitoring the temperature of the skin at the sensor site, and by knowing a value of temperature (programmed into the memory chip) at which the “motion-is-signal” algorithm can be utilized for the specific sensor design being used, improved reading accuracy through motion can be better accomplished.
- Additional Information on Use of Pins
- Contact Switch—Sensor Off
- Similar to the contact electrodes of the Nellcor FS-14 fetal sensor, an extrinsic probe of skin contact can be used to indicate whether the sensor is in adequate contact to the patient. This extrinsic probe could be accomplished, for example, through an impedance measurement across two electrodes, a force or pressure switch that is sensitive to whether adequate force or pressure is present in the sensor placement, or through other means. Dedicated sensor connector pins, or pin-sharing, could be used to accomplish this additional measure of sensor-patient contact.
- Chemical Sensor for EtO Cycles
- An electrochemical or thermal device that senses and stores to memory the number of exposures (zero, once, or potentially more than once or the actual number) to sterilization cycles could be used to capture the history of the sensor. Excessive exposure to sterilization cycles degrades a number of components in the sensor, and can affect its performance. A sensor exceeding a certain number of exposures could cause a display to indicate the sensor needs to be replaced.
- Sensor Expiration
- This need not be a separate device, but the memory could contain a date after which time the sterilization can no longer be certified as being effective. Sterilization can be sensed and the date recorded automatically by the sensor itself.
- Sensor Expiration Date/Sensor Parking: Meter
- At the time of manufacture, the expiration date of the sensor may be written into the memory chip. The memory-enabled instrument would then do something with this knowledge (e.g., indicate “expired sensor”, or refuse to function if expired). Alternately, the elapsed time of sensor usage could be tracked in the memory chip (written to it by the instrument) and the sensor would “expire” after a memory programmed maximum (greater for reusable sensors than for single-use sensors).
- Auto Shut-Off
- After sensor expiration, the instrument may refuse to function with this sensor and would indicate that a fresh sensor is needed. Furthermore, the sensor could be disabled by running a high current through it, or by other means.
- Warranty Date
- Similar to the expiration date, the date of expiration of the sensor warranty could be written into the memory chip (e.g., 2, or 6, or 12, etc. months from the date of 10 manufacture or the date of first use). The instrument would give some indication of this as appropriate.
- Patient Specific Information (Written to Sensor from Monitor)
- Trending and/or data logging of patient monitoring parameters may be stored in the memory of the memory chip. As the patient and sensor travel from ward-to-ward of the hospital., and consequently plug into different oximeters, the patient-specific data could be displayed as it is contained in the patient's dedicated sensor. Examples of the type of data are given below:
- Trending
- Low High Sat
- The lowest and/or highest SpO2 value during the monitored time, or the lowest/highest values over the past specified monitoring time (e.g., 2 hours, 1 day, etc.)
- Duration of Monitoring
- How long has the patient been monitored by the pulse oximeter? (elapsed time counter).
- Beginning and End of Monitoring
- Clock time of when the monitor was turned on and off.
- Pre-set Alarm Limits
- The alarm limits used with this patient become written to the memory chip by the instrument. This allows patient-specific alarm values to be set and memorized so that as the patient moves from monitor-to monitor (the sensor staying with the patient), the appropriate alarm limits need not be reset each time on the new monitor. Instead, this only needs to happen once, or whenever the clinician adjusts alarm limits.
- Changeable Key
- Data encryption utilizes private and/or public keys to scramble the data written to the memory chip and later decipher the data so that only authorized devices are supported. To further prevent the use with a monitor that is not certified to provide correct results, the sensor manufacturing system could periodically change the private and/or public keys. The change in the key could be communicated to the instrument via the memory chip in encrypted form. The purpose of this feature is to elevate the level of security in the memory system.
- Monitor Code Upgrades From Modem or Sensor
- Distributing code updates in memory. Whenever an oximeter notes that a code update field is present in the sensor, it would check whether the proposed update had previously been installed, and (if not) whether any indicated prerequisites were present (e.g. a code patch might not function properly in the absence of a previously-circulated patch). If appropriate conditions are met, the code upgrade would be installed. If prerequisites are missing, a message would be displayed to the user, telling him how to obtain the prerequisites (e.g. call Nellcor).
- Black Box Encoder (Patient History Serial Number of Box. etc.)
- Use the memory as a general-purpose carrier of patient data, covering not just oximetry but a lot of other information about the patient.
- Optical Efficiency Correction
- If it is desirable to know where a particular patient lies in COP space, it is useful to know the inherent brightness of LEDs, sensitivity of detector, and anything else about the particular sensor assembly (e.g. bandage color and alignment) that will affect the amount of light which the sensor receives. Given that information, a measure of the patient's optical transmissivity may be computed for each LED wavelength, which depends almost entirely on the properties of the patient. Signal to noise ratio of the oximeter is probably determined by the size of the detected signal, not by the transmissivity of the patient alone. This could take advantage of DC transmissivity of the tissue to improve the accuracy of pulse oximetry.
- Another reason for recording LED and detector parameters in the sensor memory is to provide a basis for later research on the drift of these parameters due to various environmental conditions which the sensor experiences. Parameters of interest include not only LED power and detector sensitivity, but also LED wavelengths, FWHM, and secondary emission level.
- Pigment Adjustment Feature
- For some types of sensors, the accuracy of the sensor may be different for patients with different skin color. The sensitivity of accuracy to skin color may depend on sensor model. The sensor might contain a sensitivity index, indicating how large an adjustment in readings should be made as a function of skin color. Skin color might be obtained by user entry of the data (e.g. menu selection). Another option would be for the sensor to measure skin color. One way to achieve the latter option would be to provide transmission sensors with auxiliary detector for “reflected” light. In combination with the optical efficiency information noted above, the signal levels reported by the auxiliary detector would sense to what extent the patient's skin was affecting red and IR pathlengths differently, and hence to what extent readings needed to be corrected.
- Accelerometer on Chip
- This might be used in a scheme in which the memory chip was on the bandage, not in the connector. This combines a MEMS accelerometer with any of several different chips that might usefully be placed in the sensor head, local digitizing chip, preamp chip, memory chip.
- Accelerometer data may be used to warn of the presence of motion (in which case special algorithms may be called into play or oximetry may be suspended), or actually to help correct for motion (to the extent to which we can produce algorithms which can predict physio-optic effects of known motion).
- Optical Shunt
- The amount of optical shunting could be measured for each sensor, or family of sensors. The value would be stored in the sensory memory for the monitor to read and use to adjust the processing coefficients.
- Monitor Chip Temperature
- The temperature of a red LED, in particular, affects its principal wavelength, which affects calibration. For one class of LEDs, the wavelength shifts by about 0.14 nm/C. The memory chip might contain circuitry capable of monitoring a thermistor or thermocouple, or the memory chip could be mounted in proximity to the LED (e.g. under it), so that it could sense directly the temperature of the LED, and provide a calibration correction accordingly.
- Monitor Ambient Temperature
- This might be used, e.g., in overseeing the operation of a warmed ear sensor. There is a thermal cutout in the control system of the WES, that causes operation to terminate if the sensor goes over a certain temperature. This is a component for protecting the patient against bums. If the reason for a high sensor temperature is that the environment is warm, it could be quite acceptable to continue oximetry, even though warmer operation would be shut down. In the absence of knowledge about environmental temperature, a high temperature reading might have to be assumed to mean that something was wrong with the sensor, in which case all operation might have to cease. An environmental temperature sensor in the plug could help to tell which rule to apply. Again, the memory chip could record the calibration of whatever device was used for thermometry.
- A passive component on the memory chip could be the thermometric sensor, and a resistance or voltage measuring device in the instrument could read out that sensor. Thus, ambient temperature sensing might not require that large changes be made in the memory chip.
- Temperature Amplifier/Detector
- In illuminating the skin for the purpose of making oxygen saturation measurements, some heat is generated by the LED emitters. Tests have been done to establish the maximum safe current for the LED drive which will assure that the skin temperature stays within a safe value for the worst case sensor/patient conditions. This means that in all cases the sensor will be operated at cooler than the maximum temperature but in most cases well below the maximum temperature.
- To establish the optimum signal for the measurement, it is desirable to drive the LEDs with higher current than is imposed by the above limitations. The temperature amplifier/detector would allow the LEDs to be driven to a level that still results in a safe temperature by monitoring the temperature, yet in many cases allow more drive current, and therefore higher signals, which could give better readings.
- The inexpensive thermistor devices that could be used in this application are characterized to allow the measurement to be accurate. These characterization values could be stored in the sensor where the thermistor is located. While in operation, the oximeter would be able to read the characterization values from the sensor, measure the resistance of the thermistor, and calculate accurately the temperature of the skin surface where the thermistor is located. This would keep the patient safe from bums and still provide the best signal available.
- RCAL Resistance Built Into Chip
- In legacy oximetry sensors there is a resistor which is selected and installed in the sensor connector, to correspond to the wavelength of the red LED. The wavelength difference from LED to LED has an impact on the calibration of the saturation measurement, if not compensated for. The oximeter will read the value of resistance and adjust its calculation accordingly.
- When adding the memory chip, memory compatible oximeters will be able to obtain the necessary calibration coefficients from the memory chip but the legacy instruments will still need a calibration resistor value. If the resistance were built-in to the chip and trimmed or selected at manufacture then only one device would need to be installed in the sensor connector. That would reduce the overall cost, yet keep the sensor compatible with both the legacy instruments and the new memory compatible instruments.
- Secondary Emission Measurement
- The oximeter is measuring the relative transmission of the red and infrared light through the tissue. LEDs have a characteristic called secondary emission which is indicative of the amount of light, at wavelengths other than the primary wavelength, that is being emitted. This characteristic will change the calibration of the device if not compensated for. It is possible to make an oximeter that will function within calibration if the secondary emission is known and compensated for. If the LED were characterized during manufacture and then the secondary emission values entered into the memory chip, the oximeter would be able to read those values and compensate for them so that the sensor was used properly. This would increase the range of LEDs that could be used for oximetry, reduce cost and provide better calibration across a wider range of LED emitters.
- Patient ID (Potentially as Tracking Device, Archiving Patient History, etc.)
- Currently sensors are placed on patients at one hospital site and stay with the patient from hospital site-to-site. It would be helpful to have the patient ID carried along in the sensor so that the record keeping, which occurs at each site, would be-able to link the recorded information with the patient. Without patient ID, the tracking has to be done manually. With trend information being stored in the sensor it also would be desirable to have the patient ID included so that as the patient went from location to location, the new location's staff could verify old information and be assured that it correlated with the patient they were receiving.
- Encode Contact Resistance (e.g. for Oxicliq)
- When making measurements of the resistance that is placed in the sensor for calibration information purposes, one of the factors that can influence that measurement is the contact resistance of the connectors that are between the oximeter and the resistor itself. In order to compensate for connectors that are significant in their impact on the measure, one could encode the contact resistance of the connector and subtract that algorithmically from the measured resistance to get a more accurate measurement of the resistance of the calibration resistor. This would enhance the accuracy with which the resistance measurement is made and, therefore, make the instrument less prone to inaccuracies in saturation calculation and display.
- Measure Capacitance to Balance Common Mode Rejection
- One of the interfering noise sources that plagues oximetry is that of common mode noise. This can come from the surrounding electrical environment. Other instruments, lighters, drills etc. can produce electrical fields that can couple into the cable between the patient and the oximeter. Once coupled-in, they can make measurements more difficult, less accurate, or not possible, depending on the severity of the noise. To help reduce this common mode noise, differential amplifiers are used for amplifying the signal from the sensor. These amplifiers amplify only the difference between two signal wires. Thus, if the common mode signal is coupled exactly the same into both wires, the amplifier will not amplify it because the same signal is present on both wires.
- If the two wires have different coupling to their electrical environment, then they will present different signals, and the difference will be amplified as if it were a signal. One component that influences this coupling is the capacitance of the lines to the outside world. This is affected by the manufacture of the cable, materials, twists in the wire, etc. If one measured the cables during manufacture and then stored that information in the memory chip, it could be read when the oximeter is operating. Once the capacitances for the two wires to the shield are known, the instrument could be provided with a tunable capacitance device that would then balance the two lines again and make the noise coupling to the lines better matched. This would reduce the amount of susceptibility to the external noise that got coupled into the patient cable. Reduced noise results in better measurements or the ability to make measurements at all on some patients.
- Fiber-Optic Infrared Wavelength Shift
- The relative wavelengths of the red and infrared light that is used to make the measurement in oximetry are important to know so that calibration can be maintained. In traditional LED oximetry, the LED sources are at the skin so that whatever wavelength is emitted is what is sensed by the photodiode that receives the light. The red LED is the only one that we need to characterize for accurate saturation measurements to be realized. The saturation is less sensitive to the IR wavelength as long as it stays fixed in the acceptable range that has been specified for the IR LEDs.
- When using plastic fibers for transmission of the light, there is a wavelength dependent absorption caused by the fiber. This has the effect of altering the apparent center wavelength of the IR source, which can affect calibration of the unit. By characterizing the fiber for its shift, one could then provide the proper compensation in the algorithm that calculated the saturation. This would restore the accuracy that would otherwise be lost in fiber transmission of the light.
- Inform Monitor of Extra LEDs
- There are limitations on the number and type of blood constituents that can be sensed using the two conventional LED wavelengths of the oximeter. The accuracy of the oximetry measurement can also be improved by using different wavelengths at different saturation ranges. An analysis unit could be developed that would utilize either or both of these features. To do this, it would be able to drive additional LEDs. The additional LEDs could be driven along with the traditional ones or separately. The oximeter (or additional constituent measurement unit) would provide the capability to calculate values for these other wavelengths, and the sensor would provide the additional information to allow the oximeter to make that calculation. These could be stored in the memory.
- Active Ambient Light Measurement
- One of the problems with oximetry sensors is the interference caused by ambient light in the environment. This can be made worse when a sensor comes loose or when the ambient light is extremely high in value. By characterizing the sensor, one could know what level of ambient light could be expected or tolerated, and give a warning to the user when the level has been exceeded. This would give them the opportunity to adjust the sensor, the light, or both to affect an improvement in the performance of the oximeter.
- Active Pressure Adiustment for Modulation Enhancement
- The stronger the pulsatile signal, the better the chances are of measuring the saturation accurately. One way to enhance the modulation percentage is to apply pressure in the range of the median pulsatile pressure. If this were implemented, one could use relatively low cost transducers and supply calibration coefficients in the memory to allow accurate pressure readings to be made. The memory could also contain the pressure settings and/or expected modulation enhancement capability to determine effectiveness of the pressure enhancement.
- Measure Perfusion
- The amount of perfusion affects the amount of modulation, and thus the AC signal. This affects both the percentage of modulation vs. the DC amount, and the absolute size of the modulation. The measured modulation, or other measurement of perfusion, can be stored in memory for trending or setting limits on acceptable perfusion before movement or other adjustment of the sensor is required.
- Keep Track of Last Time Sensor Moved or Disconnected
- The time of movement or disconnecting of the sensor could be written into the memory. Disconnecting can be detected from the interruption of the signal to the monitor. Moving can be detected by a sensor off detection, and a subsequent sensor on detection. Alternately, aggressive movement could be detected and interpreted as moving of the sensor, or a combination with a sensor off detection could be used.
- Identify Private Label Sensors
- A code can be stored in the sensor memory identifying the sensor manufacturer. This code can be read and used to indicate operability with monitors of other manufacturers, or to indicate any conversion algorithm that may be needed for a signal from a sensor to be used by a monitor from a different manufacturer. The code can also be used to allow only supported features to be used.
- Measure Sensor Wetness
- A moisture sensor or impedance sensor can detect the amount of wetness of the sensor. This can be used for different purposes and can be stored in the sensor memory for trending or monitoring. To determine sensor malfunction, the sensor can be disabled if the wetness exceeds a threshold, which could be stored in the sensor memory. Some sensors may not provide for isolation of the patient from the electronics for excessive wetness. The maximum allowable wetness could be stored in the sensor memory.
- Sensor Isolation Indicator
- The sensor memory could identify that the sensor provides isolation, so wetness is not a concern. Alternately, it could indicate that isolation is not provided by the sensor, or a limited amount of isolation is provided.
- Low Power Mode Identifier (Sensor Tells Oximeter to Sleep or Wake Up)
- A portable battery-powered monitor can power down when the saturation is at a good level, and the patient is stable. Minimal circuitry in the sensor could be used to do sufficient processing to tell the monitor when to wake up.
- Battery to Run Digital Chip
- A battery can be included in the sensor for a wireless connection to a monitor. Alternately, a battery could be used to continue to send data when the monitor is powered down.
- Motion Generator (“Thumper”)
- The sensor can include a cuff (which inflates and deflates) or other mechanical mechanism for inducting motion to get a signal or for inducing pulsitile blood flow to improve the signal.
- Sensor Force Indicator (e.g., Too Tight)
- A transducer can measure the amount of force on the sensor. This can be compared to a maximum value stored in the sensor memory to determine if the sensor is on too tight. The tightness can also be recorded and monitored. For example, a patient could swell, and this could be determined from the trend information and provided as information to a clinician on a display.
- Force Transducer Calibration to Get Pressure
- A calibration value can be stored in the sensor memory for converting a force measurement into a pressure measurement. A force transducer can then be used to measure pressure.
- Number of Wavelengths
- The sensor memory can store an indication of the number of wavelengths used in the sensor, and could store the wavelengths themselves.
- Drive Information
- The sensor memory can store information about when to drive which LEDs. They could all be driven at once, or a subset could be driven, for example.
- Display for Additional Wavelengths
- The memory can store information about what parameters are to be analyzed and displayed when the extra wavelengths are used. Oxygen saturation may be displayed when 2 wavelengths are used, while additional information could be displayed when an extra wavelength or more are used (Hct, COHb, etc.).
- Recycling Times
- Each time a sensor is recycled (sterilized and reconstructed), a number in the sensor memory can be incremented. This can be used to prevent operation of the sensor if it has been recycled more than the allowed number of times (e.g., 3 times).
- While the present invention has been described herein with reference to particular embodiments thereof, a latitude of modification, various changes and substitutions are intended in the foregoing disclosure, and it will be appreciated that in some instances some features of the invention will be employed without a corresponding use of other features without departing from the scope of the invention as set forth. Therefore, many modifications may be made to adapt a particular situation or material to the teachings of the invention without departing from the essential scope and spirit of the present invention. It is intended that the invention not be limited to the particular embodiments disclosed, but that the invention will include all embodiments and equivalents falling within the scope of the claims.
Claims (12)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/444,788 US20060217605A1 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US22961600P | 2000-08-31 | 2000-08-31 | |
US09/943,805 US6591123B2 (en) | 2000-08-31 | 2001-08-30 | Oximeter sensor with digital memory recording sensor data |
US10/440,560 US7085597B2 (en) | 2000-08-31 | 2003-05-16 | Oximeter sensor with digital memory recording sensor data |
US11/444,788 US20060217605A1 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/440,560 Continuation US7085597B2 (en) | 2000-08-31 | 2003-05-16 | Oximeter sensor with digital memory recording sensor data |
Publications (1)
Publication Number | Publication Date |
---|---|
US20060217605A1 true US20060217605A1 (en) | 2006-09-28 |
Family
ID=26923456
Family Applications (9)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/943,805 Expired - Lifetime US6591123B2 (en) | 2000-08-31 | 2001-08-30 | Oximeter sensor with digital memory recording sensor data |
US10/440,560 Expired - Lifetime US7085597B2 (en) | 2000-08-31 | 2003-05-16 | Oximeter sensor with digital memory recording sensor data |
US11/445,107 Expired - Fee Related US7949380B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/444,788 Abandoned US20060217605A1 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/444,949 Active 2024-10-03 US7809419B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/445,029 Active 2027-09-13 US8626256B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/444,577 Abandoned US20060217604A1 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/445,016 Active 2025-11-27 US8068889B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/445,126 Active 2026-05-14 US8639307B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
Family Applications Before (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/943,805 Expired - Lifetime US6591123B2 (en) | 2000-08-31 | 2001-08-30 | Oximeter sensor with digital memory recording sensor data |
US10/440,560 Expired - Lifetime US7085597B2 (en) | 2000-08-31 | 2003-05-16 | Oximeter sensor with digital memory recording sensor data |
US11/445,107 Expired - Fee Related US7949380B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
Family Applications After (5)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/444,949 Active 2024-10-03 US7809419B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/445,029 Active 2027-09-13 US8626256B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/444,577 Abandoned US20060217604A1 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/445,016 Active 2025-11-27 US8068889B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
US11/445,126 Active 2026-05-14 US8639307B2 (en) | 2000-08-31 | 2006-06-01 | Oximeter sensor with digital memory encoding sensor data |
Country Status (9)
Country | Link |
---|---|
US (9) | US6591123B2 (en) |
EP (1) | EP1315447B1 (en) |
JP (1) | JP2004510467A (en) |
AT (1) | ATE399503T1 (en) |
AU (1) | AU2001288697A1 (en) |
CA (1) | CA2419496C (en) |
DE (1) | DE60134649D1 (en) |
ES (1) | ES2309087T3 (en) |
WO (1) | WO2002017780A1 (en) |
Cited By (31)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20070043269A1 (en) * | 2000-08-31 | 2007-02-22 | Nellcor Puritan Bennett Inc. | Method and circuit for storing and providing historical physiological data |
US20080011652A1 (en) * | 2006-06-21 | 2008-01-17 | Dieter Takev | Screen assembly for separating material according to particle size |
US20080188727A1 (en) * | 2002-04-09 | 2008-08-07 | Benaron David A | Broadband solid-state spectroscopy illuminator and method |
US20090048502A1 (en) * | 2002-04-09 | 2009-02-19 | Benaron David A | Broadband illuminator for oximetry, hemoglobin, met-hemoglobin, carboxy-hemoglobin, and other blood component monitoring |
US20090163787A1 (en) * | 2007-12-21 | 2009-06-25 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US20090247852A1 (en) * | 2008-03-31 | 2009-10-01 | Nellcor Puritan Bennett Llc | System and method for facilitating sensor and monitor communication |
US20100081904A1 (en) * | 2008-09-30 | 2010-04-01 | Nellcor Puritan Bennett Llc | Device And Method For Securing A Medical Sensor to An Infant's Head |
US7698909B2 (en) | 2002-10-01 | 2010-04-20 | Nellcor Puritan Bennett Llc | Headband with tension indicator |
US7809420B2 (en) | 2003-06-25 | 2010-10-05 | Nellcor Puritan Bennett Llc | Hat-based oximeter sensor |
US7810359B2 (en) | 2002-10-01 | 2010-10-12 | Nellcor Puritan Bennett Llc | Headband with tension indicator |
US20110028814A1 (en) * | 2008-03-31 | 2011-02-03 | Nellcor Puritan Bennett Llc | Medical Monitoring Patch Device And Methods |
US8007441B2 (en) | 2004-03-08 | 2011-08-30 | Nellcor Puritan Bennett Llc | Pulse oximeter with alternate heart-rate determination |
US8219170B2 (en) | 2006-09-20 | 2012-07-10 | Nellcor Puritan Bennett Llc | System and method for practicing spectrophotometry using light emitting nanostructure devices |
US8257274B2 (en) | 2008-09-25 | 2012-09-04 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US8265724B2 (en) | 2007-03-09 | 2012-09-11 | Nellcor Puritan Bennett Llc | Cancellation of light shunting |
US8346328B2 (en) | 2007-12-21 | 2013-01-01 | Covidien Lp | Medical sensor and technique for using the same |
US8364220B2 (en) | 2008-09-25 | 2013-01-29 | Covidien Lp | Medical sensor and technique for using the same |
US8391941B2 (en) | 2009-07-17 | 2013-03-05 | Covidien Lp | System and method for memory switching for multiple configuration medical sensor |
US8412297B2 (en) | 2003-10-01 | 2013-04-02 | Covidien Lp | Forehead sensor placement |
US8417310B2 (en) | 2009-08-10 | 2013-04-09 | Covidien Lp | Digital switching in multi-site sensor |
US8505821B2 (en) | 2009-06-30 | 2013-08-13 | Covidien Lp | System and method for providing sensor quality assurance |
US8515515B2 (en) | 2009-03-25 | 2013-08-20 | Covidien Lp | Medical sensor with compressible light barrier and technique for using the same |
US20130275155A1 (en) * | 2012-04-12 | 2013-10-17 | Kyle William Miko | Pulse oximeters and systems and methods for obtaining data therefrom |
US8684175B2 (en) | 2006-09-22 | 2014-04-01 | Covidien Lp | Method for shipping and protecting an endotracheal tube with an inflated cuff |
US8781548B2 (en) | 2009-03-31 | 2014-07-15 | Covidien Lp | Medical sensor with flexible components and technique for using the same |
US9010634B2 (en) | 2009-06-30 | 2015-04-21 | Covidien Lp | System and method for linking patient data to a patient and providing sensor quality assurance |
USD794206S1 (en) | 2015-12-18 | 2017-08-08 | Covidien Lp | Combined strap and cradle for wearable medical monitor |
USD804042S1 (en) | 2015-12-10 | 2017-11-28 | Covidien Lp | Wearable medical monitor |
US10342485B2 (en) | 2014-10-01 | 2019-07-09 | Covidien Lp | Removable base for wearable medical monitor |
US11426103B2 (en) | 2008-07-03 | 2022-08-30 | Masimo Corporation | Multi-stream data collection system for noninvasive measurement of blood constituents |
US11638532B2 (en) | 2008-07-03 | 2023-05-02 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
Families Citing this family (132)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6018673A (en) | 1996-10-10 | 2000-01-25 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US8103325B2 (en) * | 1999-03-08 | 2012-01-24 | Tyco Healthcare Group Lp | Method and circuit for storing and providing historical physiological data |
US6675031B1 (en) | 1999-04-14 | 2004-01-06 | Mallinckrodt Inc. | Method and circuit for indicating quality and accuracy of physiological measurements |
US6591123B2 (en) * | 2000-08-31 | 2003-07-08 | Mallinckrodt Inc. | Oximeter sensor with digital memory recording sensor data |
JP4763179B2 (en) * | 2001-09-06 | 2011-08-31 | セイコーインスツル株式会社 | Pulse meter |
US6748254B2 (en) | 2001-10-12 | 2004-06-08 | Nellcor Puritan Bennett Incorporated | Stacked adhesive optical sensor |
EP1479007B1 (en) * | 2002-02-07 | 2018-01-10 | Invensys Systems, Inc. | System and method for authentication and fail-safe transmission of safety messages |
US7497827B2 (en) | 2004-07-13 | 2009-03-03 | Dexcom, Inc. | Transcutaneous analyte sensor |
US6863652B2 (en) * | 2002-03-13 | 2005-03-08 | Draeger Medical Systems, Inc. | Power conserving adaptive control system for generating signal in portable medical devices |
US7186222B1 (en) * | 2002-09-10 | 2007-03-06 | Radiant Medical, Inc. | Vascular introducer with temperature monitoring probe and systems for endovascular temperature control |
US7190986B1 (en) | 2002-10-18 | 2007-03-13 | Nellcor Puritan Bennett Inc. | Non-adhesive oximeter sensor for sensitive skin |
US7027849B2 (en) * | 2002-11-22 | 2006-04-11 | Masimo Laboratories, Inc. | Blood parameter measurement system |
JP2007526017A (en) * | 2003-06-25 | 2007-09-13 | エイセル インコーポレイテッド | Matrix composition tailored for tissue repair |
US7500950B2 (en) | 2003-07-25 | 2009-03-10 | Masimo Corporation | Multipurpose sensor port |
US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
US7630747B2 (en) * | 2003-09-09 | 2009-12-08 | Keimar, Inc. | Apparatus for ascertaining blood characteristics and probe for use therewith |
US9247900B2 (en) | 2004-07-13 | 2016-02-02 | Dexcom, Inc. | Analyte sensor |
US8615282B2 (en) | 2004-07-13 | 2013-12-24 | Dexcom, Inc. | Analyte sensor |
US7438683B2 (en) * | 2004-03-04 | 2008-10-21 | Masimo Corporation | Application identification sensor |
US7341560B2 (en) * | 2004-10-05 | 2008-03-11 | Rader, Fishman & Grauer Pllc | Apparatuses and methods for non-invasively monitoring blood parameters |
US7359742B2 (en) * | 2004-11-12 | 2008-04-15 | Nonin Medical, Inc. | Sensor assembly |
US7392074B2 (en) * | 2005-01-21 | 2008-06-24 | Nonin Medical, Inc. | Sensor system with memory and method of using same |
US7957780B2 (en) | 2005-03-01 | 2011-06-07 | Masimo Laboratories, Inc. | Physiological parameter confidence measure |
US8133178B2 (en) | 2006-02-22 | 2012-03-13 | Dexcom, Inc. | Analyte sensor |
US7657295B2 (en) | 2005-08-08 | 2010-02-02 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7590439B2 (en) | 2005-08-08 | 2009-09-15 | Nellcor Puritan Bennett Llc | Bi-stable medical sensor and technique for using the same |
US7657294B2 (en) | 2005-08-08 | 2010-02-02 | Nellcor Puritan Bennett Llc | Compliant diaphragm medical sensor and technique for using the same |
US20070060808A1 (en) | 2005-09-12 | 2007-03-15 | Carine Hoarau | Medical sensor for reducing motion artifacts and technique for using the same |
US8092379B2 (en) * | 2005-09-29 | 2012-01-10 | Nellcor Puritan Bennett Llc | Method and system for determining when to reposition a physiological sensor |
US7904130B2 (en) | 2005-09-29 | 2011-03-08 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7899510B2 (en) | 2005-09-29 | 2011-03-01 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7869850B2 (en) | 2005-09-29 | 2011-01-11 | Nellcor Puritan Bennett Llc | Medical sensor for reducing motion artifacts and technique for using the same |
US8062221B2 (en) | 2005-09-30 | 2011-11-22 | Nellcor Puritan Bennett Llc | Sensor for tissue gas detection and technique for using the same |
US7483731B2 (en) | 2005-09-30 | 2009-01-27 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7486979B2 (en) | 2005-09-30 | 2009-02-03 | Nellcor Puritan Bennett Llc | Optically aligned pulse oximetry sensor and technique for using the same |
US7881762B2 (en) | 2005-09-30 | 2011-02-01 | Nellcor Puritan Bennett Llc | Clip-style medical sensor and technique for using the same |
US8233954B2 (en) | 2005-09-30 | 2012-07-31 | Nellcor Puritan Bennett Llc | Mucosal sensor for the assessment of tissue and blood constituents and technique for using the same |
US7555327B2 (en) | 2005-09-30 | 2009-06-30 | Nellcor Puritan Bennett Llc | Folding medical sensor and technique for using the same |
JP2007244736A (en) * | 2006-03-17 | 2007-09-27 | Toshiba Corp | Living body component measuring device and method |
US8073518B2 (en) | 2006-05-02 | 2011-12-06 | Nellcor Puritan Bennett Llc | Clip-style medical sensor and technique for using the same |
US10188348B2 (en) | 2006-06-05 | 2019-01-29 | Masimo Corporation | Parameter upgrade system |
US8145288B2 (en) | 2006-08-22 | 2012-03-27 | Nellcor Puritan Bennett Llc | Medical sensor for reducing signal artifacts and technique for using the same |
US8396527B2 (en) | 2006-09-22 | 2013-03-12 | Covidien Lp | Medical sensor for reducing signal artifacts and technique for using the same |
US8195264B2 (en) | 2006-09-22 | 2012-06-05 | Nellcor Puritan Bennett Llc | Medical sensor for reducing signal artifacts and technique for using the same |
US8175671B2 (en) | 2006-09-22 | 2012-05-08 | Nellcor Puritan Bennett Llc | Medical sensor for reducing signal artifacts and technique for using the same |
US7869849B2 (en) | 2006-09-26 | 2011-01-11 | Nellcor Puritan Bennett Llc | Opaque, electrically nonconductive region on a medical sensor |
KR100758987B1 (en) * | 2006-09-26 | 2007-09-17 | 삼성전자주식회사 | A led lighting device and a method for controlling the same |
US7574245B2 (en) | 2006-09-27 | 2009-08-11 | Nellcor Puritan Bennett Llc | Flexible medical sensor enclosure |
US7796403B2 (en) | 2006-09-28 | 2010-09-14 | Nellcor Puritan Bennett Llc | Means for mechanical registration and mechanical-electrical coupling of a faraday shield to a photodetector and an electrical circuit |
US7890153B2 (en) | 2006-09-28 | 2011-02-15 | Nellcor Puritan Bennett Llc | System and method for mitigating interference in pulse oximetry |
US7706896B2 (en) * | 2006-09-29 | 2010-04-27 | Nellcor Puritan Bennett Llc | User interface and identification in a medical device system and method |
US8175667B2 (en) | 2006-09-29 | 2012-05-08 | Nellcor Puritan Bennett Llc | Symmetric LED array for pulse oximetry |
US7476131B2 (en) | 2006-09-29 | 2009-01-13 | Nellcor Puritan Bennett Llc | Device for reducing crosstalk |
US8068891B2 (en) | 2006-09-29 | 2011-11-29 | Nellcor Puritan Bennett Llc | Symmetric LED array for pulse oximetry |
US20080081956A1 (en) * | 2006-09-29 | 2008-04-03 | Jayesh Shah | System and method for integrating voice with a medical device |
US7684842B2 (en) | 2006-09-29 | 2010-03-23 | Nellcor Puritan Bennett Llc | System and method for preventing sensor misuse |
US7680522B2 (en) | 2006-09-29 | 2010-03-16 | Nellcor Puritan Bennett Llc | Method and apparatus for detecting misapplied sensors |
US20080097175A1 (en) * | 2006-09-29 | 2008-04-24 | Boyce Robin S | System and method for display control of patient monitor |
US7925511B2 (en) * | 2006-09-29 | 2011-04-12 | Nellcor Puritan Bennett Llc | System and method for secure voice identification in a medical device |
US7698002B2 (en) * | 2006-09-29 | 2010-04-13 | Nellcor Puritan Bennett Llc | Systems and methods for user interface and identification in a medical device |
US20080082338A1 (en) * | 2006-09-29 | 2008-04-03 | O'neil Michael P | Systems and methods for secure voice identification and medical device interface |
US7880626B2 (en) | 2006-10-12 | 2011-02-01 | Masimo Corporation | System and method for monitoring the life of a physiological sensor |
US8255026B1 (en) * | 2006-10-12 | 2012-08-28 | Masimo Corporation, Inc. | Patient monitor capable of monitoring the quality of attached probes and accessories |
US8265723B1 (en) | 2006-10-12 | 2012-09-11 | Cercacor Laboratories, Inc. | Oximeter probe off indicator defining probe off space |
US8280469B2 (en) | 2007-03-09 | 2012-10-02 | Nellcor Puritan Bennett Llc | Method for detection of aberrant tissue spectra |
US7894869B2 (en) | 2007-03-09 | 2011-02-22 | Nellcor Puritan Bennett Llc | Multiple configuration medical sensor and technique for using the same |
US8346327B2 (en) * | 2007-03-09 | 2013-01-01 | Covidien Lp | Method for identification of sensor site by local skin spectrum data |
US8221326B2 (en) * | 2007-03-09 | 2012-07-17 | Nellcor Puritan Bennett Llc | Detection of oximetry sensor sites based on waveform characteristics |
US20080221418A1 (en) * | 2007-03-09 | 2008-09-11 | Masimo Corporation | Noninvasive multi-parameter patient monitor |
EP2139383B1 (en) | 2007-03-27 | 2013-02-13 | Masimo Laboratories, Inc. | Multiple wavelength optical sensor |
US8374665B2 (en) | 2007-04-21 | 2013-02-12 | Cercacor Laboratories, Inc. | Tissue profile wellness monitor |
US8100893B2 (en) * | 2007-11-28 | 2012-01-24 | The Spectranetics Corporation | Laser catheter calibrator |
US8366613B2 (en) | 2007-12-26 | 2013-02-05 | Covidien Lp | LED drive circuit for pulse oximetry and method for using same |
US8577434B2 (en) | 2007-12-27 | 2013-11-05 | Covidien Lp | Coaxial LED light sources |
US8442608B2 (en) | 2007-12-28 | 2013-05-14 | Covidien Lp | System and method for estimating physiological parameters by deconvolving artifacts |
US8452364B2 (en) | 2007-12-28 | 2013-05-28 | Covidien LLP | System and method for attaching a sensor to a patient's skin |
US8897850B2 (en) | 2007-12-31 | 2014-11-25 | Covidien Lp | Sensor with integrated living hinge and spring |
US8199007B2 (en) | 2007-12-31 | 2012-06-12 | Nellcor Puritan Bennett Llc | Flex circuit snap track for a biometric sensor |
US8070508B2 (en) | 2007-12-31 | 2011-12-06 | Nellcor Puritan Bennett Llc | Method and apparatus for aligning and securing a cable strain relief |
US8092993B2 (en) | 2007-12-31 | 2012-01-10 | Nellcor Puritan Bennett Llc | Hydrogel thin film for use as a biosensor |
US8437822B2 (en) | 2008-03-28 | 2013-05-07 | Covidien Lp | System and method for estimating blood analyte concentration |
US8112375B2 (en) | 2008-03-31 | 2012-02-07 | Nellcor Puritan Bennett Llc | Wavelength selection and outlier detection in reduced rank linear models |
US7880884B2 (en) | 2008-06-30 | 2011-02-01 | Nellcor Puritan Bennett Llc | System and method for coating and shielding electronic sensor components |
US8071935B2 (en) | 2008-06-30 | 2011-12-06 | Nellcor Puritan Bennett Llc | Optical detector with an overmolded faraday shield |
US7887345B2 (en) | 2008-06-30 | 2011-02-15 | Nellcor Puritan Bennett Llc | Single use connector for pulse oximetry sensors |
US20100010328A1 (en) * | 2008-07-11 | 2010-01-14 | Nguyen Harry D | Probes and sensors for ascertaining blood characteristics and methods and devices for use therewith |
US8308355B2 (en) * | 2008-07-29 | 2012-11-13 | Welch Allyn, Inc. | Cycle counting |
WO2010027957A2 (en) * | 2008-09-03 | 2010-03-11 | Keimar, Inc. | Systems for characterizing physiologic parameters and methods for use therewith |
US8417309B2 (en) | 2008-09-30 | 2013-04-09 | Covidien Lp | Medical sensor |
US8914088B2 (en) | 2008-09-30 | 2014-12-16 | Covidien Lp | Medical sensor and technique for using the same |
US8423112B2 (en) | 2008-09-30 | 2013-04-16 | Covidien Lp | Medical sensor and technique for using the same |
US9404961B2 (en) * | 2008-12-09 | 2016-08-02 | Covidien Lp | System and method of determining light source aging |
US8452366B2 (en) | 2009-03-16 | 2013-05-28 | Covidien Lp | Medical monitoring device with flexible circuitry |
US8221319B2 (en) | 2009-03-25 | 2012-07-17 | Nellcor Puritan Bennett Llc | Medical device for assessing intravascular blood volume and technique for using the same |
US8509869B2 (en) | 2009-05-15 | 2013-08-13 | Covidien Lp | Method and apparatus for detecting and analyzing variations in a physiologic parameter |
US8571619B2 (en) | 2009-05-20 | 2013-10-29 | Masimo Corporation | Hemoglobin display and patient treatment |
US8634891B2 (en) | 2009-05-20 | 2014-01-21 | Covidien Lp | Method and system for self regulation of sensor component contact pressure |
US8311601B2 (en) | 2009-06-30 | 2012-11-13 | Nellcor Puritan Bennett Llc | Reflectance and/or transmissive pulse oximeter |
US8378832B2 (en) | 2009-07-09 | 2013-02-19 | Harry J. Cassidy | Breathing disorder treatment system and method |
US8428675B2 (en) | 2009-08-19 | 2013-04-23 | Covidien Lp | Nanofiber adhesives used in medical devices |
US8514086B2 (en) | 2009-08-31 | 2013-08-20 | Abbott Diabetes Care Inc. | Displays for a medical device |
US9066660B2 (en) | 2009-09-29 | 2015-06-30 | Nellcor Puritan Bennett Ireland | Systems and methods for high-pass filtering a photoplethysmograph signal |
US9839381B1 (en) | 2009-11-24 | 2017-12-12 | Cercacor Laboratories, Inc. | Physiological measurement system with automatic wavelength adjustment |
US8801613B2 (en) | 2009-12-04 | 2014-08-12 | Masimo Corporation | Calibration for multi-stage physiological monitors |
US9775545B2 (en) | 2010-09-28 | 2017-10-03 | Masimo Corporation | Magnetic electrical connector for patient monitors |
WO2012050847A2 (en) | 2010-09-28 | 2012-04-19 | Masimo Corporation | Depth of consciousness monitor including oximeter |
GB201018417D0 (en) * | 2010-11-01 | 2010-12-15 | Gas Sensing Solutions Ltd | Apparatus and method for generating light pulses from LEDs in optical absorption gas sensors |
US8521247B2 (en) * | 2010-12-29 | 2013-08-27 | Covidien Lp | Certification apparatus and method for a medical device computer |
US20120271121A1 (en) * | 2010-12-29 | 2012-10-25 | Basis Science, Inc. | Integrated Biometric Sensing and Display Device |
US8610769B2 (en) | 2011-02-28 | 2013-12-17 | Covidien Lp | Medical monitor data collection system and method |
US9030211B2 (en) | 2011-11-30 | 2015-05-12 | Covidien Lp | Calibration resistance emulator |
US9192330B2 (en) | 2012-02-27 | 2015-11-24 | Covidien Lp | System and method for storing and providing patient-related data |
US9907494B2 (en) * | 2012-04-18 | 2018-03-06 | Hutchinson Technology Incorporated | NIRS device with optical wavelength and path length correction |
US9157773B2 (en) | 2012-05-31 | 2015-10-13 | General Electric Company | Sensor validation method, patient monitor, physiological sensor, and computer program product for a patient monitor |
WO2014085602A1 (en) | 2012-11-29 | 2014-06-05 | Abbott Diabetes Care Inc. | Methods, devices, and systems related to analyte monitoring |
US9351688B2 (en) | 2013-01-29 | 2016-05-31 | Covidien Lp | Low power monitoring systems and method |
US20150051463A1 (en) * | 2013-08-16 | 2015-02-19 | Guy P. Curtis | Oximetry Signal, Pulse-Pressure Correlator |
US10371395B2 (en) * | 2014-06-03 | 2019-08-06 | Trane International Inc. | System and method for a compressor dome temperature sensor location verification |
JP5727074B1 (en) * | 2014-06-04 | 2015-06-03 | 長谷川電機工業株式会社 | DC voltage detector |
WO2016057553A1 (en) | 2014-10-07 | 2016-04-14 | Masimo Corporation | Modular physiological sensors |
TWI517838B (en) * | 2014-10-23 | 2016-01-21 | 陳孝文 | Apparatus of sensing blood flow and method thereof |
CN105534531A (en) * | 2014-10-29 | 2016-05-04 | 上海华博信息服务有限公司 | Method and system for preventing fatigue driving |
US10213121B2 (en) | 2015-02-19 | 2019-02-26 | Covidien Lp | Physiological monitoring methods and systems utilizing distributed algorithms |
US10342467B2 (en) * | 2015-03-11 | 2019-07-09 | Nonin Medical, Inc. | Segmented sensor |
CN108135543A (en) * | 2015-09-28 | 2018-06-08 | 皇家飞利浦有限公司 | The pulse oximetry of safety, monitor are connected with cloud |
US9826912B2 (en) | 2015-11-11 | 2017-11-28 | Livassured B.V. | Photoplethysmographic device for measuring a heart rhythm |
US11361864B2 (en) | 2015-11-24 | 2022-06-14 | Koninklijke Philips N.V. | Tracking usage of a pulse oximeter via a network system |
TWI765885B (en) * | 2016-04-21 | 2022-06-01 | 美商菲歐普提斯公司 | Method and device for determining tissue oxygen saturation with melanin correction |
AU2017278133B2 (en) | 2016-06-07 | 2022-06-09 | Stryker Corporation | Thermal control system |
US20180353111A1 (en) * | 2017-06-09 | 2018-12-13 | Covidien Lp | Systems and methods for driving optical sensors |
US10722117B2 (en) * | 2018-01-22 | 2020-07-28 | Covidien Lp | Systems and methods for storing data on medical sensors |
CA3102030A1 (en) * | 2018-06-01 | 2019-12-05 | Nonin Medical, Inc. | Oximetry system self-test |
Citations (83)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3720199A (en) * | 1971-05-14 | 1973-03-13 | Avco Corp | Safety connector for balloon pump |
US3790910A (en) * | 1972-04-21 | 1974-02-05 | Garrett Corp | Conditioning circuit and method for variable frequency sensor |
US4303984A (en) * | 1979-12-14 | 1981-12-01 | Honeywell Inc. | Sensor output correction circuit |
US4446715A (en) * | 1982-06-07 | 1984-05-08 | Camino Laboratories, Inc. | Transducer calibration system |
US4621643A (en) * | 1982-09-02 | 1986-11-11 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4653498A (en) * | 1982-09-13 | 1987-03-31 | Nellcor Incorporated | Pulse oximeter monitor |
US4684245A (en) * | 1985-10-28 | 1987-08-04 | Oximetrix, Inc. | Electro-optical coupler for catheter oximeter |
US4700708A (en) * | 1982-09-02 | 1987-10-20 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4714080A (en) * | 1986-10-06 | 1987-12-22 | Nippon Colin Co., Ltd. | Method and apparatus for noninvasive monitoring of arterial blood oxygen saturation |
US4734873A (en) * | 1984-02-02 | 1988-03-29 | Honeywell Inc. | Method of digital process variable transmitter calibration and a process variable transmitter system utilizing the same |
US4845649A (en) * | 1984-12-19 | 1989-07-04 | Robert Bosch Gmbh | Sensor for measuring physical dimensions and process for balancing the sensor |
US4858615A (en) * | 1981-11-10 | 1989-08-22 | Sentron V.O.F. | Catheter sensor and memory unit |
US4862872A (en) * | 1987-04-17 | 1989-09-05 | Olympus Optical Co., Ltd. | Endoscope and endoscope washing apparatus |
US4868476A (en) * | 1987-10-30 | 1989-09-19 | Hewlett-Packard Company | Transducer with integral memory |
US4942877A (en) * | 1986-09-05 | 1990-07-24 | Minolta Camera Kabushiki Kaisha | Device for measuring oxygen saturation degree in arterial blood |
US5008843A (en) * | 1987-12-23 | 1991-04-16 | Dr. Ing. H.C.F. Porsche Ag | Sensor having an answerback device |
US5016198A (en) * | 1986-04-25 | 1991-05-14 | Siemens Aktiengesellschaft | Measuring system that allocates a measured value to a measurable variable and measurment transducer thereof |
US5025791A (en) * | 1989-06-28 | 1991-06-25 | Colin Electronics Co., Ltd. | Pulse oximeter with physical motion sensor |
US5058588A (en) * | 1989-09-19 | 1991-10-22 | Hewlett-Packard Company | Oximeter and medical sensor therefor |
US5070732A (en) * | 1987-09-17 | 1991-12-10 | Square D Company | Modular sensor device |
US5162725A (en) * | 1989-08-21 | 1992-11-10 | Alnor Instrument Company | Modular metering instrument including multiple sensing probes |
US5226417A (en) * | 1991-03-11 | 1993-07-13 | Nellcor, Inc. | Apparatus for the detection of motion transients |
US5246003A (en) * | 1991-08-28 | 1993-09-21 | Nellcor Incorporated | Disposable pulse oximeter sensor |
US5259381A (en) * | 1986-08-18 | 1993-11-09 | Physio-Control Corporation | Apparatus for the automatic calibration of signals employed in oximetry |
US5329931A (en) * | 1989-02-21 | 1994-07-19 | William L. Clauson | Apparatus and method for automatic stimulation of mammals in response to blood gas analysis |
US5341291A (en) * | 1987-12-09 | 1994-08-23 | Arch Development Corporation | Portable medical interactive test selector having plug-in replaceable memory |
US5347476A (en) * | 1992-11-25 | 1994-09-13 | Mcbean Sr Ronald V | Instrumentation system with multiple sensor modules |
US5360005A (en) * | 1992-01-10 | 1994-11-01 | Wilk Peter J | Medical diagnosis device for sensing cardiac activity and blood flow |
US5368026A (en) * | 1993-03-26 | 1994-11-29 | Nellcor Incorporated | Oximeter with motion detection for alarm modification |
US5371128A (en) * | 1994-01-14 | 1994-12-06 | Dow Corning Corporation | Hot-melt silicone pressure sensitive adhesive with siloxylated allyloxypropane diol copolymers as additives |
US5372141A (en) * | 1992-07-01 | 1994-12-13 | Body Composition Analyzers, Inc. | Body composition analyzer |
US5385144A (en) * | 1992-07-23 | 1995-01-31 | Minolta Co., Ltd. | Respiration diagnosis apparatus |
US5429129A (en) * | 1991-08-22 | 1995-07-04 | Sensor Devices, Inc. | Apparatus for determining spectral absorption by a specific substance in a fluid |
US5431170A (en) * | 1990-05-26 | 1995-07-11 | Mathews; Geoffrey R. | Pulse responsive device |
US5443801A (en) * | 1990-07-20 | 1995-08-22 | Kew Import/Export Inc. | Endoscope cleaner/sterilizer |
US5448991A (en) * | 1989-11-01 | 1995-09-12 | Polson; Michael J. R. | Method of measuring the oxygen saturation in pulsating blood flow |
US5513646A (en) * | 1992-11-09 | 1996-05-07 | I Am Fine, Inc. | Personal security monitoring system and method |
US5528519A (en) * | 1993-05-20 | 1996-06-18 | Otax Co., Ltd. | Connector for measuring apparatus |
US5627531A (en) * | 1994-09-30 | 1997-05-06 | Ohmeda Inc. | Multi-function menu selection device |
US5645059A (en) * | 1993-12-17 | 1997-07-08 | Nellcor Incorporated | Medical sensor with modulated encoding scheme |
US5645060A (en) * | 1995-06-14 | 1997-07-08 | Nellcor Puritan Bennett Incorporated | Method and apparatus for removing artifact and noise from pulse oximetry |
US5660176A (en) * | 1993-12-29 | 1997-08-26 | First Opinion Corporation | Computerized medical diagnostic and treatment advice system |
US5660163A (en) * | 1993-11-19 | 1997-08-26 | Alfred E. Mann Foundation For Scientific Research | Glucose sensor assembly |
US5678448A (en) * | 1994-01-14 | 1997-10-21 | Fullen Systems, Inc. | System for continuously measuring forces applied by the foot |
US5718235A (en) * | 1992-10-06 | 1998-02-17 | Gw Scientific, Inc. | Detection of abnormal and induction of normal heart rate variability |
US5720293A (en) * | 1991-01-29 | 1998-02-24 | Baxter International Inc. | Diagnostic catheter with memory |
US5800350A (en) * | 1993-11-01 | 1998-09-01 | Polartechnics, Limited | Apparatus for tissue type recognition |
US5818583A (en) * | 1996-11-08 | 1998-10-06 | Purdue Research Foundation | Particle analysis system and method |
US5830121A (en) * | 1993-10-27 | 1998-11-03 | Asahi Kogaku Kogyo Kabushiki Kaisha | Endoscopic apparatus having an endoscope and a peripheral device wherein total usage of the endoscope is quantified and recorded |
US5855609A (en) * | 1992-08-24 | 1999-01-05 | Lipomatrix, Incorporated (Bvi) | Medical information transponder implant and tracking system |
US5865736A (en) * | 1997-09-30 | 1999-02-02 | Nellcor Puritan Bennett, Inc. | Method and apparatus for nuisance alarm reductions |
US5954644A (en) * | 1997-03-24 | 1999-09-21 | Ohmeda Inc. | Method for ambient light subtraction in a photoplethysmographic measurement instrument |
US5964701A (en) * | 1996-10-24 | 1999-10-12 | Massachusetts Institute Of Technology | Patient monitoring finger ring sensor |
US5987343A (en) * | 1997-11-07 | 1999-11-16 | Datascope Investment Corp. | Method for storing pulse oximetry sensor characteristics |
US5995859A (en) * | 1994-02-14 | 1999-11-30 | Nihon Kohden Corporation | Method and apparatus for accurately measuring the saturated oxygen in arterial blood by substantially eliminating noise from the measurement signal |
US6004276A (en) * | 1997-03-03 | 1999-12-21 | Quinton Instrument Company | Open architecture cardiology information system |
US6018673A (en) * | 1996-10-10 | 2000-01-25 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US6023541A (en) * | 1995-12-20 | 2000-02-08 | Nellcor Puritan Bennett Incorporated | Active optical oximeter probe adapter |
US6095984A (en) * | 1996-04-17 | 2000-08-01 | Seiko Epson Corporation | Arrhythmia detecting apparatus |
US6104938A (en) * | 1996-06-12 | 2000-08-15 | Instrumentarium Oy | Procedure, apparatus and detector for the determination of fractional oxygen saturation |
US6122536A (en) * | 1995-07-06 | 2000-09-19 | Animas Corporation | Implantable sensor and system for measurement and control of blood constituent levels |
US6298252B1 (en) * | 1998-09-29 | 2001-10-02 | Mallinckrodt, Inc. | Oximeter sensor with encoder connected to detector |
US6298255B1 (en) * | 1999-06-09 | 2001-10-02 | Aspect Medical Systems, Inc. | Smart electrophysiological sensor system with automatic authentication and validation and an interface for a smart electrophysiological sensor system |
US6308089B1 (en) * | 1999-04-14 | 2001-10-23 | O.B. Scientific, Inc. | Limited use medical probe |
US6356774B1 (en) * | 1998-09-29 | 2002-03-12 | Mallinckrodt, Inc. | Oximeter sensor with encoded temperature characteristic |
US6360114B1 (en) * | 1999-03-25 | 2002-03-19 | Masimo Corporation | Pulse oximeter probe-off detector |
US6377829B1 (en) * | 1999-12-09 | 2002-04-23 | Masimo Corporation | Resposable pulse oximetry sensor |
US6405087B1 (en) * | 2000-02-25 | 2002-06-11 | Pacesetter, Inc. | Cardiac stimulation system providing implantable device performance evaluation and method |
US6463310B1 (en) * | 1999-03-08 | 2002-10-08 | Mallinckrodt, Inc. | Method and circuit for storing and providing historical physiological data |
US6553241B2 (en) * | 2000-08-31 | 2003-04-22 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding sensor expiration data |
US6591123B2 (en) * | 2000-08-31 | 2003-07-08 | Mallinckrodt Inc. | Oximeter sensor with digital memory recording sensor data |
US20030135099A1 (en) * | 1999-12-09 | 2003-07-17 | Ammar Al-Ali | Isolation and communication element for a resposable pulse oximetry sensor |
US6600940B1 (en) * | 2000-08-31 | 2003-07-29 | Mallinckrodt Inc. | Oximeter sensor with digital memory |
US6606510B2 (en) * | 2000-08-31 | 2003-08-12 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding patient data |
US6609834B2 (en) * | 1997-05-13 | 2003-08-26 | Agilent Technologies, Inc. | Multimode communications systems |
US6628975B1 (en) * | 2000-08-31 | 2003-09-30 | Mallinckrodt Inc. | Oximeter sensor with digital memory storing data |
US6708049B1 (en) * | 1999-09-28 | 2004-03-16 | Nellcor Puritan Bennett Incorporated | Sensor with signature of data relating to sensor |
US6801797B2 (en) * | 2000-04-17 | 2004-10-05 | Nellcor Puritan Bennett Incorporated | Pulse oximeter sensor with piece-wise function |
US20050165323A1 (en) * | 1999-10-07 | 2005-07-28 | Lamont, Llc. | Physiological signal monitoring apparatus and method |
US6934571B2 (en) * | 1998-08-14 | 2005-08-23 | Bioasyst, L.L.C. | Integrated physiologic sensor system |
US6979812B2 (en) * | 1999-08-26 | 2005-12-27 | Masimo Corporation | Systems and methods for indicating an amount of use of a sensor |
US6988056B2 (en) * | 1997-04-24 | 2006-01-17 | Bright Ideas, L.L.C. | Signal interpretation engine |
US20060030764A1 (en) * | 1999-04-14 | 2006-02-09 | Mallinckrodt Inc. | Method and circuit for indicating quality and accuracy of physiological measurements |
Family Cites Families (37)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3797479A (en) * | 1972-04-14 | 1974-03-19 | Comprehensive Health Testing L | Spirometer |
US4041935A (en) * | 1974-03-07 | 1977-08-16 | Vitalograph (Ireland) Limited | Device for breathing measurement |
US4210155A (en) * | 1978-08-03 | 1980-07-01 | Jerry Grimes | Inspirational inhalation spirometer apparatus |
DE3028061A1 (en) | 1980-07-24 | 1982-09-09 | Günter 2093 Stelle Eikhof | Fitness training calculator - has slide disc allowing performance achieved to be converted into assessment of fitness level |
DE3502410A1 (en) * | 1985-01-25 | 1986-07-31 | Robert Bosch Gmbh, 7000 Stuttgart | ELECTROMAGNETICALLY ACTUABLE FUEL INJECTION VALVE |
US4684246A (en) * | 1985-06-26 | 1987-08-04 | Downing Elizabeth A | Soft contact lens analyzer |
US4913150A (en) * | 1986-08-18 | 1990-04-03 | Physio-Control Corporation | Method and apparatus for the automatic calibration of signals employed in oximetry |
US4845873A (en) * | 1988-05-02 | 1989-07-11 | Hazlett Stephen E | Animal decoy with movable appendage |
US5007423A (en) * | 1989-10-04 | 1991-04-16 | Nippon Colin Company Ltd. | Oximeter sensor temperature control |
GB2247838B (en) | 1990-09-04 | 1994-06-15 | Glaxo Group Ltd | Peak flow meter |
US5233520A (en) | 1990-12-19 | 1993-08-03 | The United States Of America As Represented By The Secretary Of Agriculture | Method and system for measurement of intake of foods, nutrients and other food components in the diet |
EP0606356B1 (en) | 1991-10-01 | 1998-06-03 | Interflo Medical, Inc. | A diagnostic catheter with memory |
WO1993006775A1 (en) | 1991-10-03 | 1993-04-15 | Medtronic, Inc. | Method and apparatus for determining oxygen saturation |
US5682877A (en) | 1991-12-30 | 1997-11-04 | Mondry; Adolph J. | System and method for automatically maintaining a blood oxygen saturation level |
EP0640978A3 (en) * | 1993-08-31 | 1998-10-07 | Ohmeda Inc. | Non-invasive software update apparatus |
DE4329898A1 (en) * | 1993-09-04 | 1995-04-06 | Marcus Dr Besson | Wireless medical diagnostic and monitoring device |
US5425375A (en) * | 1993-09-09 | 1995-06-20 | Cardiac Pathways Corporation | Reusable medical device with usage memory, system using same |
EP0684575A4 (en) * | 1993-12-14 | 1997-05-14 | Mochida Pharm Co Ltd | Medical measuring apparatus. |
US5471382A (en) | 1994-01-10 | 1995-11-28 | Informed Access Systems, Inc. | Medical network management system and process |
US5830135A (en) | 1994-03-31 | 1998-11-03 | Bosque; Elena M. | Fuzzy logic alarm system for pulse oximeters |
US5645069A (en) * | 1994-05-26 | 1997-07-08 | Lg Electronics Inc. | System for and method of analyzing electrocardiograms employing chaos techniques |
US5758644A (en) * | 1995-06-07 | 1998-06-02 | Masimo Corporation | Manual and automatic probe calibration |
US5790432A (en) * | 1995-08-21 | 1998-08-04 | Solar Light Company, Inc. | Universal measuring instrument with signal processing algorithm encapsulated into interchangeable intelligent detectors |
US5961446A (en) * | 1995-10-06 | 1999-10-05 | Tevital Incorporated | Patient terminal for home health care system |
AU720597B2 (en) | 1996-02-15 | 2000-06-08 | Biosense, Inc. | Catheter calibration and usage monitoring system |
JP3939782B2 (en) | 1996-07-05 | 2007-07-04 | 株式会社島津製作所 | Light scatterer measurement device |
WO1998020323A1 (en) * | 1996-11-08 | 1998-05-14 | Purdue Research Foundation | Particle analysis system and method |
US6363175B1 (en) * | 1997-04-02 | 2002-03-26 | Sonyx, Inc. | Spectral encoding of information |
JPH10314149A (en) * | 1997-05-20 | 1998-12-02 | Casio Comput Co Ltd | Probe exchangeable electric measurement device, probe management method and pulse oximeter |
US6466808B1 (en) * | 1999-11-22 | 2002-10-15 | Mallinckrodt Inc. | Single device for both heating and temperature measurement in an oximeter sensor |
JP3623096B2 (en) * | 1998-02-09 | 2005-02-23 | 住友電工ハイテックス株式会社 | Calibration method for transdermal blood gas monitor |
US6246966B1 (en) | 1998-04-06 | 2001-06-12 | Bayer Corporation | Method and apparatus for data management authentication in a clinical analyzer |
US6442755B1 (en) | 1998-07-07 | 2002-08-27 | United Video Properties, Inc. | Electronic program guide using markup language |
JP4038280B2 (en) | 1998-09-14 | 2008-01-23 | シスメックス株式会社 | Non-invasive biological component measuring device |
US8103325B2 (en) | 1999-03-08 | 2012-01-24 | Tyco Healthcare Group Lp | Method and circuit for storing and providing historical physiological data |
US6241679B1 (en) | 1999-05-24 | 2001-06-05 | Medwave, Inc. | Non-invasive blood pressure sensing device and method using transducer with associate memory |
US7046687B1 (en) * | 2002-01-16 | 2006-05-16 | Tau Networks | Configurable virtual output queues in a scalable switching system |
-
2001
- 2001-08-30 US US09/943,805 patent/US6591123B2/en not_active Expired - Lifetime
- 2001-08-31 DE DE60134649T patent/DE60134649D1/en not_active Expired - Lifetime
- 2001-08-31 AT AT01968451T patent/ATE399503T1/en not_active IP Right Cessation
- 2001-08-31 AU AU2001288697A patent/AU2001288697A1/en not_active Abandoned
- 2001-08-31 CA CA2419496A patent/CA2419496C/en not_active Expired - Lifetime
- 2001-08-31 EP EP01968451A patent/EP1315447B1/en not_active Expired - Lifetime
- 2001-08-31 ES ES01968451T patent/ES2309087T3/en not_active Expired - Lifetime
- 2001-08-31 JP JP2002522761A patent/JP2004510467A/en active Pending
- 2001-08-31 WO PCT/US2001/027417 patent/WO2002017780A1/en active Application Filing
-
2003
- 2003-05-16 US US10/440,560 patent/US7085597B2/en not_active Expired - Lifetime
-
2006
- 2006-06-01 US US11/445,107 patent/US7949380B2/en not_active Expired - Fee Related
- 2006-06-01 US US11/444,788 patent/US20060217605A1/en not_active Abandoned
- 2006-06-01 US US11/444,949 patent/US7809419B2/en active Active
- 2006-06-01 US US11/445,029 patent/US8626256B2/en active Active
- 2006-06-01 US US11/444,577 patent/US20060217604A1/en not_active Abandoned
- 2006-06-01 US US11/445,016 patent/US8068889B2/en active Active
- 2006-06-01 US US11/445,126 patent/US8639307B2/en active Active
Patent Citations (101)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3720199A (en) * | 1971-05-14 | 1973-03-13 | Avco Corp | Safety connector for balloon pump |
US3790910A (en) * | 1972-04-21 | 1974-02-05 | Garrett Corp | Conditioning circuit and method for variable frequency sensor |
US4303984A (en) * | 1979-12-14 | 1981-12-01 | Honeywell Inc. | Sensor output correction circuit |
US4858615A (en) * | 1981-11-10 | 1989-08-22 | Sentron V.O.F. | Catheter sensor and memory unit |
US4446715A (en) * | 1982-06-07 | 1984-05-08 | Camino Laboratories, Inc. | Transducer calibration system |
US4446715B1 (en) * | 1982-06-07 | 1991-09-17 | Camino Lab Inc | |
US4621643A (en) * | 1982-09-02 | 1986-11-11 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4700708A (en) * | 1982-09-02 | 1987-10-20 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4653498A (en) * | 1982-09-13 | 1987-03-31 | Nellcor Incorporated | Pulse oximeter monitor |
US4653498B1 (en) * | 1982-09-13 | 1989-04-18 | ||
US4734873A (en) * | 1984-02-02 | 1988-03-29 | Honeywell Inc. | Method of digital process variable transmitter calibration and a process variable transmitter system utilizing the same |
US4845649A (en) * | 1984-12-19 | 1989-07-04 | Robert Bosch Gmbh | Sensor for measuring physical dimensions and process for balancing the sensor |
US4684245A (en) * | 1985-10-28 | 1987-08-04 | Oximetrix, Inc. | Electro-optical coupler for catheter oximeter |
US5016198A (en) * | 1986-04-25 | 1991-05-14 | Siemens Aktiengesellschaft | Measuring system that allocates a measured value to a measurable variable and measurment transducer thereof |
US5259381A (en) * | 1986-08-18 | 1993-11-09 | Physio-Control Corporation | Apparatus for the automatic calibration of signals employed in oximetry |
US4942877A (en) * | 1986-09-05 | 1990-07-24 | Minolta Camera Kabushiki Kaisha | Device for measuring oxygen saturation degree in arterial blood |
US4714080A (en) * | 1986-10-06 | 1987-12-22 | Nippon Colin Co., Ltd. | Method and apparatus for noninvasive monitoring of arterial blood oxygen saturation |
US4862872A (en) * | 1987-04-17 | 1989-09-05 | Olympus Optical Co., Ltd. | Endoscope and endoscope washing apparatus |
US5070732A (en) * | 1987-09-17 | 1991-12-10 | Square D Company | Modular sensor device |
US4868476A (en) * | 1987-10-30 | 1989-09-19 | Hewlett-Packard Company | Transducer with integral memory |
US5341291A (en) * | 1987-12-09 | 1994-08-23 | Arch Development Corporation | Portable medical interactive test selector having plug-in replaceable memory |
US5008843A (en) * | 1987-12-23 | 1991-04-16 | Dr. Ing. H.C.F. Porsche Ag | Sensor having an answerback device |
US5329931A (en) * | 1989-02-21 | 1994-07-19 | William L. Clauson | Apparatus and method for automatic stimulation of mammals in response to blood gas analysis |
US5025791A (en) * | 1989-06-28 | 1991-06-25 | Colin Electronics Co., Ltd. | Pulse oximeter with physical motion sensor |
US5162725A (en) * | 1989-08-21 | 1992-11-10 | Alnor Instrument Company | Modular metering instrument including multiple sensing probes |
US5058588A (en) * | 1989-09-19 | 1991-10-22 | Hewlett-Packard Company | Oximeter and medical sensor therefor |
US5448991A (en) * | 1989-11-01 | 1995-09-12 | Polson; Michael J. R. | Method of measuring the oxygen saturation in pulsating blood flow |
US5431170A (en) * | 1990-05-26 | 1995-07-11 | Mathews; Geoffrey R. | Pulse responsive device |
US5443801A (en) * | 1990-07-20 | 1995-08-22 | Kew Import/Export Inc. | Endoscope cleaner/sterilizer |
US5720293A (en) * | 1991-01-29 | 1998-02-24 | Baxter International Inc. | Diagnostic catheter with memory |
US5226417A (en) * | 1991-03-11 | 1993-07-13 | Nellcor, Inc. | Apparatus for the detection of motion transients |
US5429129A (en) * | 1991-08-22 | 1995-07-04 | Sensor Devices, Inc. | Apparatus for determining spectral absorption by a specific substance in a fluid |
US5246003A (en) * | 1991-08-28 | 1993-09-21 | Nellcor Incorporated | Disposable pulse oximeter sensor |
US5360005A (en) * | 1992-01-10 | 1994-11-01 | Wilk Peter J | Medical diagnosis device for sensing cardiac activity and blood flow |
US5372141A (en) * | 1992-07-01 | 1994-12-13 | Body Composition Analyzers, Inc. | Body composition analyzer |
US5385144A (en) * | 1992-07-23 | 1995-01-31 | Minolta Co., Ltd. | Respiration diagnosis apparatus |
US5855609A (en) * | 1992-08-24 | 1999-01-05 | Lipomatrix, Incorporated (Bvi) | Medical information transponder implant and tracking system |
US5718235A (en) * | 1992-10-06 | 1998-02-17 | Gw Scientific, Inc. | Detection of abnormal and induction of normal heart rate variability |
US5513646A (en) * | 1992-11-09 | 1996-05-07 | I Am Fine, Inc. | Personal security monitoring system and method |
US5365462A (en) * | 1992-11-25 | 1994-11-15 | Mcbean Sr Ronald V | Instrumentation system with multiple sensor modules providing calibration date information |
US5347476A (en) * | 1992-11-25 | 1994-09-13 | Mcbean Sr Ronald V | Instrumentation system with multiple sensor modules |
US5368026A (en) * | 1993-03-26 | 1994-11-29 | Nellcor Incorporated | Oximeter with motion detection for alarm modification |
US5528519A (en) * | 1993-05-20 | 1996-06-18 | Otax Co., Ltd. | Connector for measuring apparatus |
US5830121A (en) * | 1993-10-27 | 1998-11-03 | Asahi Kogaku Kogyo Kabushiki Kaisha | Endoscopic apparatus having an endoscope and a peripheral device wherein total usage of the endoscope is quantified and recorded |
US5800350A (en) * | 1993-11-01 | 1998-09-01 | Polartechnics, Limited | Apparatus for tissue type recognition |
US5660163A (en) * | 1993-11-19 | 1997-08-26 | Alfred E. Mann Foundation For Scientific Research | Glucose sensor assembly |
US6044283A (en) * | 1993-12-17 | 2000-03-28 | Nellcor Puritan Bennett Incorporated | Medical sensor with modulated encoding scheme |
US5645059A (en) * | 1993-12-17 | 1997-07-08 | Nellcor Incorporated | Medical sensor with modulated encoding scheme |
US5660176A (en) * | 1993-12-29 | 1997-08-26 | First Opinion Corporation | Computerized medical diagnostic and treatment advice system |
US5678448A (en) * | 1994-01-14 | 1997-10-21 | Fullen Systems, Inc. | System for continuously measuring forces applied by the foot |
US5371128A (en) * | 1994-01-14 | 1994-12-06 | Dow Corning Corporation | Hot-melt silicone pressure sensitive adhesive with siloxylated allyloxypropane diol copolymers as additives |
US5995859A (en) * | 1994-02-14 | 1999-11-30 | Nihon Kohden Corporation | Method and apparatus for accurately measuring the saturated oxygen in arterial blood by substantially eliminating noise from the measurement signal |
US5627531A (en) * | 1994-09-30 | 1997-05-06 | Ohmeda Inc. | Multi-function menu selection device |
US5645060A (en) * | 1995-06-14 | 1997-07-08 | Nellcor Puritan Bennett Incorporated | Method and apparatus for removing artifact and noise from pulse oximetry |
US6122536A (en) * | 1995-07-06 | 2000-09-19 | Animas Corporation | Implantable sensor and system for measurement and control of blood constituent levels |
US6023541A (en) * | 1995-12-20 | 2000-02-08 | Nellcor Puritan Bennett Incorporated | Active optical oximeter probe adapter |
US6095984A (en) * | 1996-04-17 | 2000-08-01 | Seiko Epson Corporation | Arrhythmia detecting apparatus |
US6104938A (en) * | 1996-06-12 | 2000-08-15 | Instrumentarium Oy | Procedure, apparatus and detector for the determination of fractional oxygen saturation |
US20050070773A1 (en) * | 1996-10-10 | 2005-03-31 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US6018673A (en) * | 1996-10-10 | 2000-01-25 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US6845256B2 (en) * | 1996-10-10 | 2005-01-18 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US20020103423A1 (en) * | 1996-10-10 | 2002-08-01 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US20050070775A1 (en) * | 1996-10-10 | 2005-03-31 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US6374129B1 (en) * | 1996-10-10 | 2002-04-16 | Nellocr Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US5964701A (en) * | 1996-10-24 | 1999-10-12 | Massachusetts Institute Of Technology | Patient monitoring finger ring sensor |
US5818583A (en) * | 1996-11-08 | 1998-10-06 | Purdue Research Foundation | Particle analysis system and method |
US6004276A (en) * | 1997-03-03 | 1999-12-21 | Quinton Instrument Company | Open architecture cardiology information system |
US5954644A (en) * | 1997-03-24 | 1999-09-21 | Ohmeda Inc. | Method for ambient light subtraction in a photoplethysmographic measurement instrument |
US6988056B2 (en) * | 1997-04-24 | 2006-01-17 | Bright Ideas, L.L.C. | Signal interpretation engine |
US6609834B2 (en) * | 1997-05-13 | 2003-08-26 | Agilent Technologies, Inc. | Multimode communications systems |
US5865736A (en) * | 1997-09-30 | 1999-02-02 | Nellcor Puritan Bennett, Inc. | Method and apparatus for nuisance alarm reductions |
US5987343A (en) * | 1997-11-07 | 1999-11-16 | Datascope Investment Corp. | Method for storing pulse oximetry sensor characteristics |
US6934571B2 (en) * | 1998-08-14 | 2005-08-23 | Bioasyst, L.L.C. | Integrated physiologic sensor system |
US6356774B1 (en) * | 1998-09-29 | 2002-03-12 | Mallinckrodt, Inc. | Oximeter sensor with encoded temperature characteristic |
US6298252B1 (en) * | 1998-09-29 | 2001-10-02 | Mallinckrodt, Inc. | Oximeter sensor with encoder connected to detector |
US6463310B1 (en) * | 1999-03-08 | 2002-10-08 | Mallinckrodt, Inc. | Method and circuit for storing and providing historical physiological data |
US6360114B1 (en) * | 1999-03-25 | 2002-03-19 | Masimo Corporation | Pulse oximeter probe-off detector |
US6308089B1 (en) * | 1999-04-14 | 2001-10-23 | O.B. Scientific, Inc. | Limited use medical probe |
US20060161054A1 (en) * | 1999-04-14 | 2006-07-20 | Reuss James L | Limited use medical probe |
US7048687B1 (en) * | 1999-04-14 | 2006-05-23 | Ob Scientific, Inc. | Limited use medical probe |
US20060030764A1 (en) * | 1999-04-14 | 2006-02-09 | Mallinckrodt Inc. | Method and circuit for indicating quality and accuracy of physiological measurements |
US6298255B1 (en) * | 1999-06-09 | 2001-10-02 | Aspect Medical Systems, Inc. | Smart electrophysiological sensor system with automatic authentication and validation and an interface for a smart electrophysiological sensor system |
US6979812B2 (en) * | 1999-08-26 | 2005-12-27 | Masimo Corporation | Systems and methods for indicating an amount of use of a sensor |
US6708049B1 (en) * | 1999-09-28 | 2004-03-16 | Nellcor Puritan Bennett Incorporated | Sensor with signature of data relating to sensor |
US20050165323A1 (en) * | 1999-10-07 | 2005-07-28 | Lamont, Llc. | Physiological signal monitoring apparatus and method |
US20030135099A1 (en) * | 1999-12-09 | 2003-07-17 | Ammar Al-Ali | Isolation and communication element for a resposable pulse oximetry sensor |
US6950687B2 (en) * | 1999-12-09 | 2005-09-27 | Masimo Corporation | Isolation and communication element for a resposable pulse oximetry sensor |
US6377829B1 (en) * | 1999-12-09 | 2002-04-23 | Masimo Corporation | Resposable pulse oximetry sensor |
US6405087B1 (en) * | 2000-02-25 | 2002-06-11 | Pacesetter, Inc. | Cardiac stimulation system providing implantable device performance evaluation and method |
US20060030763A1 (en) * | 2000-04-17 | 2006-02-09 | Nellcor Puritan Bennett Incorporated | Pulse oximeter sensor with piece-wise function |
US6801797B2 (en) * | 2000-04-17 | 2004-10-05 | Nellcor Puritan Bennett Incorporated | Pulse oximeter sensor with piece-wise function |
US6553241B2 (en) * | 2000-08-31 | 2003-04-22 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding sensor expiration data |
US20040006261A1 (en) * | 2000-08-31 | 2004-01-08 | Nellcor Puritan Bennett Inc. | Oximeter sensor with digital memory encoding patient data |
US6628975B1 (en) * | 2000-08-31 | 2003-09-30 | Mallinckrodt Inc. | Oximeter sensor with digital memory storing data |
US6591123B2 (en) * | 2000-08-31 | 2003-07-08 | Mallinckrodt Inc. | Oximeter sensor with digital memory recording sensor data |
US20060030765A1 (en) * | 2000-08-31 | 2006-02-09 | David Swedlow | Oximeter sensor with digital memory encoding patient data |
US20060030762A1 (en) * | 2000-08-31 | 2006-02-09 | Swedlow David | Oximeter sensor with digital memory encoding patient data |
US6606510B2 (en) * | 2000-08-31 | 2003-08-12 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding patient data |
US6600940B1 (en) * | 2000-08-31 | 2003-07-29 | Mallinckrodt Inc. | Oximeter sensor with digital memory |
US7085597B2 (en) * | 2000-08-31 | 2006-08-01 | Mallinckrodt, Inc. | Oximeter sensor with digital memory recording sensor data |
US20060217604A1 (en) * | 2000-08-31 | 2006-09-28 | Nellcor Puritan Bennett Inc. | Oximeter sensor with digital memory encoding sensor data |
Cited By (61)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US10806406B2 (en) | 2000-08-31 | 2020-10-20 | Covidien Lp | Method and circuit for storing and providing historical physiological data |
US20070043269A1 (en) * | 2000-08-31 | 2007-02-22 | Nellcor Puritan Bennett Inc. | Method and circuit for storing and providing historical physiological data |
US9844348B2 (en) | 2000-08-31 | 2017-12-19 | Coviden Lp | Method and circuit for storing and providing historical physiological data |
US20110220943A1 (en) * | 2002-04-09 | 2011-09-15 | Spectros Corporation | Quantum Dot LED Device And Method |
US20090048502A1 (en) * | 2002-04-09 | 2009-02-19 | Benaron David A | Broadband illuminator for oximetry, hemoglobin, met-hemoglobin, carboxy-hemoglobin, and other blood component monitoring |
US20110133086A1 (en) * | 2002-04-09 | 2011-06-09 | Spectros Corporation | White LED For Illumination With Additional Light Source For Analysis |
US20090187086A1 (en) * | 2002-04-09 | 2009-07-23 | Benaron David A | Integrated White LED Illuminator and Color Sensor Detector System and Method |
US20080287758A1 (en) * | 2002-04-09 | 2008-11-20 | Benaron David A | Illuminator probe with memory device and method |
US20080188727A1 (en) * | 2002-04-09 | 2008-08-07 | Benaron David A | Broadband solid-state spectroscopy illuminator and method |
US7698909B2 (en) | 2002-10-01 | 2010-04-20 | Nellcor Puritan Bennett Llc | Headband with tension indicator |
US7810359B2 (en) | 2002-10-01 | 2010-10-12 | Nellcor Puritan Bennett Llc | Headband with tension indicator |
US7822453B2 (en) | 2002-10-01 | 2010-10-26 | Nellcor Puritan Bennett Llc | Forehead sensor placement |
US7899509B2 (en) | 2002-10-01 | 2011-03-01 | Nellcor Puritan Bennett Llc | Forehead sensor placement |
US8452367B2 (en) | 2002-10-01 | 2013-05-28 | Covidien Lp | Forehead sensor placement |
US7809420B2 (en) | 2003-06-25 | 2010-10-05 | Nellcor Puritan Bennett Llc | Hat-based oximeter sensor |
US7813779B2 (en) | 2003-06-25 | 2010-10-12 | Nellcor Puritan Bennett Llc | Hat-based oximeter sensor |
US7877127B2 (en) | 2003-06-25 | 2011-01-25 | Nellcor Puritan Bennett Llc | Hat-based oximeter sensor |
US7877126B2 (en) | 2003-06-25 | 2011-01-25 | Nellcor Puritan Bennett Llc | Hat-based oximeter sensor |
US7979102B2 (en) | 2003-06-25 | 2011-07-12 | Nellcor Puritan Bennett Llc | Hat-based oximeter sensor |
US8412297B2 (en) | 2003-10-01 | 2013-04-02 | Covidien Lp | Forehead sensor placement |
US8007441B2 (en) | 2004-03-08 | 2011-08-30 | Nellcor Puritan Bennett Llc | Pulse oximeter with alternate heart-rate determination |
US20080011652A1 (en) * | 2006-06-21 | 2008-01-17 | Dieter Takev | Screen assembly for separating material according to particle size |
US8219170B2 (en) | 2006-09-20 | 2012-07-10 | Nellcor Puritan Bennett Llc | System and method for practicing spectrophotometry using light emitting nanostructure devices |
US8684175B2 (en) | 2006-09-22 | 2014-04-01 | Covidien Lp | Method for shipping and protecting an endotracheal tube with an inflated cuff |
US9642576B2 (en) | 2007-03-09 | 2017-05-09 | Covidien Lp | Cancellation of light shunting |
US8265724B2 (en) | 2007-03-09 | 2012-09-11 | Nellcor Puritan Bennett Llc | Cancellation of light shunting |
US8923944B2 (en) | 2007-03-09 | 2014-12-30 | Covidien Lp | Cancellation of light shunting |
US8346328B2 (en) | 2007-12-21 | 2013-01-01 | Covidien Lp | Medical sensor and technique for using the same |
US8352004B2 (en) | 2007-12-21 | 2013-01-08 | Covidien Lp | Medical sensor and technique for using the same |
US20090163787A1 (en) * | 2007-12-21 | 2009-06-25 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US9693718B2 (en) | 2008-03-31 | 2017-07-04 | Covidien Lp | System and method for facilitating sensor and monitor communication |
US20110028814A1 (en) * | 2008-03-31 | 2011-02-03 | Nellcor Puritan Bennett Llc | Medical Monitoring Patch Device And Methods |
US20090247852A1 (en) * | 2008-03-31 | 2009-10-01 | Nellcor Puritan Bennett Llc | System and method for facilitating sensor and monitor communication |
US8983566B2 (en) * | 2008-03-31 | 2015-03-17 | Covidien Lp | System and method for facilitating sensor and monitor communication |
US8364224B2 (en) * | 2008-03-31 | 2013-01-29 | Covidien Lp | System and method for facilitating sensor and monitor communication |
US20130267806A1 (en) * | 2008-03-31 | 2013-10-10 | Covidien Lp | System and method for facilitating sensor and monitor communication |
US8750954B2 (en) | 2008-03-31 | 2014-06-10 | Covidien Lp | Medical monitoring patch device and methods |
US11642037B2 (en) | 2008-07-03 | 2023-05-09 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US12036009B1 (en) | 2008-07-03 | 2024-07-16 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US12023139B1 (en) | 2008-07-03 | 2024-07-02 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US11426103B2 (en) | 2008-07-03 | 2022-08-30 | Masimo Corporation | Multi-stream data collection system for noninvasive measurement of blood constituents |
US11484230B2 (en) * | 2008-07-03 | 2022-11-01 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US11751773B2 (en) | 2008-07-03 | 2023-09-12 | Masimo Corporation | Emitter arrangement for physiological measurements |
US11484229B2 (en) | 2008-07-03 | 2022-11-01 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US11638532B2 (en) | 2008-07-03 | 2023-05-02 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US11647914B2 (en) | 2008-07-03 | 2023-05-16 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US11642036B2 (en) | 2008-07-03 | 2023-05-09 | Masimo Corporation | User-worn device for noninvasively measuring a physiological parameter of a user |
US8364220B2 (en) | 2008-09-25 | 2013-01-29 | Covidien Lp | Medical sensor and technique for using the same |
US8257274B2 (en) | 2008-09-25 | 2012-09-04 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US20100081904A1 (en) * | 2008-09-30 | 2010-04-01 | Nellcor Puritan Bennett Llc | Device And Method For Securing A Medical Sensor to An Infant's Head |
US8515515B2 (en) | 2009-03-25 | 2013-08-20 | Covidien Lp | Medical sensor with compressible light barrier and technique for using the same |
US8781548B2 (en) | 2009-03-31 | 2014-07-15 | Covidien Lp | Medical sensor with flexible components and technique for using the same |
US9010634B2 (en) | 2009-06-30 | 2015-04-21 | Covidien Lp | System and method for linking patient data to a patient and providing sensor quality assurance |
US8505821B2 (en) | 2009-06-30 | 2013-08-13 | Covidien Lp | System and method for providing sensor quality assurance |
US8391941B2 (en) | 2009-07-17 | 2013-03-05 | Covidien Lp | System and method for memory switching for multiple configuration medical sensor |
US8417310B2 (en) | 2009-08-10 | 2013-04-09 | Covidien Lp | Digital switching in multi-site sensor |
US20140187886A1 (en) * | 2012-04-12 | 2014-07-03 | Kyle William Miko | Pulse oximeters and systems and methods for obtaining data therefrom |
US20130275155A1 (en) * | 2012-04-12 | 2013-10-17 | Kyle William Miko | Pulse oximeters and systems and methods for obtaining data therefrom |
US10342485B2 (en) | 2014-10-01 | 2019-07-09 | Covidien Lp | Removable base for wearable medical monitor |
USD804042S1 (en) | 2015-12-10 | 2017-11-28 | Covidien Lp | Wearable medical monitor |
USD794206S1 (en) | 2015-12-18 | 2017-08-08 | Covidien Lp | Combined strap and cradle for wearable medical monitor |
Also Published As
Publication number | Publication date |
---|---|
AU2001288697A1 (en) | 2002-03-13 |
ES2309087T3 (en) | 2008-12-16 |
DE60134649D1 (en) | 2008-08-14 |
US8639307B2 (en) | 2014-01-28 |
CA2419496A1 (en) | 2002-03-07 |
ATE399503T1 (en) | 2008-07-15 |
US6591123B2 (en) | 2003-07-08 |
US20020038081A1 (en) | 2002-03-28 |
CA2419496C (en) | 2012-01-17 |
US7085597B2 (en) | 2006-08-01 |
US20060229510A1 (en) | 2006-10-12 |
US20060217608A1 (en) | 2006-09-28 |
US8068889B2 (en) | 2011-11-29 |
WO2002017780A1 (en) | 2002-03-07 |
JP2004510467A (en) | 2004-04-08 |
US7809419B2 (en) | 2010-10-05 |
US8626256B2 (en) | 2014-01-07 |
US20060217606A1 (en) | 2006-09-28 |
US20060229511A1 (en) | 2006-10-12 |
US20060217607A1 (en) | 2006-09-28 |
US7949380B2 (en) | 2011-05-24 |
US20030195402A1 (en) | 2003-10-16 |
EP1315447B1 (en) | 2008-07-02 |
US20060217604A1 (en) | 2006-09-28 |
EP1315447A1 (en) | 2003-06-04 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US8068889B2 (en) | Oximeter sensor with digital memory encoding sensor data | |
US10806406B2 (en) | Method and circuit for storing and providing historical physiological data | |
US20060224059A1 (en) | Method and circuit for storing and providing historical physiological data |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: MALLINCKRODT INC., MISSOURI Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:FEIN, MICHAEL E.;MANNHEIMER, PAUL D.;MERCHANT, ADNAN;AND OTHERS;SIGNING DATES FROM 20011101 TO 20011105;REEL/FRAME:027008/0151 |
|
AS | Assignment |
Owner name: TYCO HEALTHCARE GROUP LP, MASSACHUSETTS Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:MALLINCKRODT INC.;REEL/FRAME:027011/0088 Effective date: 20110623 |
|
AS | Assignment |
Owner name: COVIDIEN LP, MASSACHUSETTS Free format text: CHANGE OF NAME;ASSIGNOR:TYCO HEALTHCARE GROUP LP;REEL/FRAME:029450/0604 Effective date: 20120928 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |