WO2005082241A1 - Oximeter cross-talk reduction - Google Patents
Oximeter cross-talk reduction Download PDFInfo
- Publication number
- WO2005082241A1 WO2005082241A1 PCT/US2005/006316 US2005006316W WO2005082241A1 WO 2005082241 A1 WO2005082241 A1 WO 2005082241A1 US 2005006316 W US2005006316 W US 2005006316W WO 2005082241 A1 WO2005082241 A1 WO 2005082241A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- signal
- cross
- talk
- red
- oximeter
- Prior art date
Links
Classifications
-
- 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7235—Details of waveform analysis
- A61B5/725—Details of waveform analysis using specific filters therefor, e.g. Kalman or adaptive filters
Definitions
- the present invention relates to oximeters, and in particular to methods for reducing cross-talk between red and IR signals in pulse oximeters.
- Pulse oximetry is typically used to measure various blood chemistry 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 scatters light through a portion of the patient's tissue where blood perfuses the tissue, and photoelectrically senses the abso ⁇ tion of light at various wavelengths in such tissue. The amount of light absorbed is then used to calculate the amount of blood constituent being measured.
- the light scattered 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 scattered through the tissue will vary in accordance with the changing amount of blood constituent in the tissue and the related light abso ⁇ tion.
- such sensors For measuring blood oxygen level, such sensors have typically been provided with a light source that is adapted to generate light of at least two different wavelengths, and with photodetectors sensitive to both of those wavelengths, in accordance with known techniques for measuring blood oxygen saturation.
- Known non-invasive sensors include devices that are secured to a portion of the body, such as a finger, an ear or the scalp. In animals and humans, the tissue of these body portions is perfused with blood and the tissue surface is readily accessible to the sensor.
- a typical pulse oximeter will alternately illuminate the patient with red and infrared light to obtain two different detector signals.
- One of the issues with each signal, for the red and infrared (IR) is cross-talk.
- the red signal after filtering, will still be tailing off when the IR LED is turned on, and vice- versa.
- pulse oximeter circuits include such filters to filter out noise before demodulating, such as the 50 or 60Hz ambient light from fluorescent or other lights, or electrical interference. Such filtering can result in crosstalk when the filtering spreads out the red and IR pulses so they overlap.
- the present invention provides a method and apparatus for reducing cross-talk in an oximeter.
- the oximeter includes a band pass filter.
- the amount of cross-talk through the band pass filter is estimated. Based on this estimate, the corner frequencies of the band pass filter are adjusted to minimize the cross-talk.
- the band pass filter is a hardware filter, and the corner frequencies are adjusted in the design and selection of the appropriate resistors and capacitors.
- the band pass filter is in hardware, and the frequencies can be adjusted during operation or calibration.
- the present invention also includes a calibration mode which is performed when a sensor is attached to the oximeter.
- the signals are measured with first only the red LED on and then with only the IR LED on. Any signal measured in the off channel is assumed to be a result of cross-talk from the other channel. The effect is linear, enabling it to be compensated for in software.
- the magnitude of the cross-talk is determined as a percentage, and subsequently the percentage is multiplied by the actual signal and subtracted from the other LED signal as cross-talk compensation.
- Fig. 1 is a block diagram of an oximeter inco ⁇ orating the present invention.
- Fig. 2 is a block diagram of a portion of the circuit of Fig. 1 illustrating the placement of a filter according to the present invention.
- Fig. 3 is a circuit diagram of a band pass filter according to an embodiment of the invention.
- Fig. 4 is a timing diagram illustrating the low and high pass filtering effects on the red and IR signals according to an embodiment of the invention.
- Fig. 5 is a circuit diagram illustrating an embodiment of a LED drive circuit including the circuit connections for the calibration mode according to an embodiment of the invention.
- FIG. 1 illustrates an embodiment of an oximetry system inco ⁇ orating the present invention.
- a sensor 10 includes red and infrared LEDs and a photodetector. These are connected by a cable 12 to a board 14. LED drive current is provided by an LED drive interface 16. The received photocurrent from the sensor is provided to an I-N interface 18.
- the IR and red voltages are then provided to a sigma-delta interface 20 inco ⁇ orating the present invention.
- the output of sigma-delta interface 20 is provided to a microcontroller 22.
- Microcontroller 22 includes flash memory for a program, and SRAM memory for data.
- the processor also includes a microprocessor chip 24 connected to a flash memory 26.
- a clock 28 is used and an interface 30 to a digital calibration in the sensor 10 is provided.
- a separate host 32 receives the processed information, as well as receiving an analog signal on a line 34 for providing an analog display.
- Fig. 2 is a block diagram illustrating the location of the filter according to an embodiment of the invention. Shown is a sensor 10 that is driven by an LED drive circuit 16. The LED drive circuit 16 alternately drives an IR LED 40 and a red LED 42. A photodetector 44 provides a signal to a current-to-voltage (l-V converter 46). The voltage signal is provided to high pass and anti-aliasing filter 48. This block includes the band pass filter according to an embodiment of the invention. The output signal is then provided to a sigma-delta modulator 50. The output of sigma-delta modulator 50 is provided to a demodulator 52, which is then provided to filtering and decimating blocks 54 and 56.
- l-V converter 46 current-to-voltage
- l-V converter 46 current-to-voltage
- This block includes the band pass filter according to an embodiment of the invention.
- the output signal is then provided to a sigma-delta modulator 50.
- Fig. 3 illustrates a band pass filter 60 according to an embodiment of the invention.
- the filter includes an amplifier 62 and a resistor and capacitor circuit comprising capacitors C2, CI 10, CI 11, and C40 and resistors R7, Rl 11, Rl 12, Rl 10, and R109.
- An input to this circuit is provided from l-V converter 46 along a line 64 to a first switch 66 for an offset correction not relevant to the present invention.
- the signal is then provided to a second switch 68, which is used for a calibration mode according to the present invention.
- a crosstalk control signal 70 couples the switch to an LED current sense line 72 for calibration mode.
- the corner frequencies are adjusted by varying the capacitor and resistor values to offset and minimize the cross-talk effect.
- the corner frequencies are the high pass and low pass ends of the band pass filter, which is in place to filter out ambient interferences.
- any filtering spreads out the signal in the time domain for example some of the IR pulse will leak into the dark pulse following it.
- Tuning the band pass filter to optimize for cross-talk is done when it is designed by adjusting the high pass filter corner and the low pass corner to force the cross-talk to be zero.
- the size of the Red pulse is measured by comparing the sample P5 (see Fig. 4) to the samples taken in the dark states P4 and P6.
- the corners are adjusted so that the high pass and low pass signals shown in Fig. 5 are adjusted so that the effect of the high pass filtering compensates for the effect of the low pass filtering to minimize cross-talk.
- the low pass filter causes a positive cross-talk
- the high pass filter causes an offsetting negative cross-talk.
- the band pass filter consists of an RC high pass followed by a Salen-Key low pass configured as a second order Butterworth filter.
- the impedance of the RC high pass section will have an effect on the transfer function of the Salen-Key circuit, however this effect is negligible if capacitance C2 is much larger than CI 10 and CI 11.
- the high pass filter cut off frequency is 32 Hz.
- the low pass filter cut off frequency is 12.7 kHz.
- Fig. 5 is a circuit diagram of an embodiment of LED drive circuit 16 of Fig. 2. Included in the circuit are a connection to the red LED on a line 80, and a connection to the IR LED on a line 82. These are provided through MOSFET transistors 84 and 86 to a 1 ohm resistor 88. In the calibration mode, the LED current sense signal on line 72 is taken from the current through this 1 ohm resistor with line 72 of Fig. 5 connected to line 72 of Fig. 3 as an input through switch 68 to the band pass filter.
- connection of line 72 in Fig. 5 during a calibration mode allows a further correction for crosstalk using a cross-talk calibration test.
- a 50% drive signal is applied to the LEDs during the calibration circuit to give a sufficiently large signal without going to full range and risking too high of a signal being provided. Alternately, other percentages of the drive current could be used.
- the present invention could be embodied in other specific forms without departing from the essential characteristic thereof.
- the drive current could be obtained in a different manner and a different design could be used for the band pass filter.
- the band pass filter could be used alone, without the software calibration added. Accordingly, the foregoing description is intended to be illustrative, but not limiting, on the scope of the invention which is set forth in the following claims.
Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU2005216981A AU2005216981A1 (en) | 2004-02-25 | 2005-02-24 | Oximeter cross-talk reduction |
JP2007500780A JP4701235B2 (en) | 2004-02-25 | 2005-02-24 | Oxygen concentration meter crosstalk reduction |
CA002556744A CA2556744A1 (en) | 2004-02-25 | 2005-02-24 | Oximeter cross-talk reduction |
MXPA06009756A MXPA06009756A (en) | 2004-02-25 | 2005-02-24 | Oximeter cross-talk reduction. |
EP05731575A EP1722677A1 (en) | 2004-02-25 | 2005-02-24 | Oximeter cross-talk reduction |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/787,541 US7215985B2 (en) | 2004-02-25 | 2004-02-25 | Oximeter cross-talk reduction |
US10/787,541 | 2004-02-25 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2005082241A1 true WO2005082241A1 (en) | 2005-09-09 |
Family
ID=34861915
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2005/006316 WO2005082241A1 (en) | 2004-02-25 | 2005-02-24 | Oximeter cross-talk reduction |
Country Status (8)
Country | Link |
---|---|
US (1) | US7215985B2 (en) |
EP (1) | EP1722677A1 (en) |
JP (1) | JP4701235B2 (en) |
CN (1) | CN1937952A (en) |
AU (1) | AU2005216981A1 (en) |
CA (1) | CA2556744A1 (en) |
MX (1) | MXPA06009756A (en) |
WO (1) | WO2005082241A1 (en) |
Cited By (1)
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---|---|---|---|---|
EP3406194A1 (en) * | 2017-05-23 | 2018-11-28 | Ams Ag | Circuit arrangement for an optical monitoring system and method for optical monitoring |
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US7761127B2 (en) | 2005-03-01 | 2010-07-20 | Masimo Laboratories, Inc. | Multiple wavelength sensor substrate |
US7400310B2 (en) * | 2005-11-28 | 2008-07-15 | Draeger Medical Systems, Inc. | Pulse signal drive circuit |
US8265724B2 (en) | 2007-03-09 | 2012-09-11 | Nellcor Puritan Bennett Llc | Cancellation of light shunting |
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 |
US8204567B2 (en) * | 2007-12-13 | 2012-06-19 | Nellcor Puritan Bennett Llc | Signal demodulation |
US8380272B2 (en) * | 2007-12-21 | 2013-02-19 | Covidien Lp | Physiological sensor |
US8366613B2 (en) | 2007-12-26 | 2013-02-05 | Covidien Lp | LED drive circuit for pulse oximetry and method for using same |
EP2262414A1 (en) * | 2008-03-31 | 2010-12-22 | Nellcor Puritan Bennett LLC | Medical monitoring patch device and methods |
US20090247846A1 (en) * | 2008-04-01 | 2009-10-01 | General Electric Company | Pulse oximeter with reduced cross talk effects |
US20100004518A1 (en) | 2008-07-03 | 2010-01-07 | Masimo Laboratories, Inc. | Heat sink for noninvasive medical sensor |
US8630691B2 (en) | 2008-08-04 | 2014-01-14 | Cercacor Laboratories, Inc. | Multi-stream sensor front ends for noninvasive measurement of blood constituents |
US20100087714A1 (en) * | 2008-10-03 | 2010-04-08 | Nellcor Puritan Bennett Ireland | Reducing cross-talk in a measurement system |
US9404961B2 (en) * | 2008-12-09 | 2016-08-02 | Covidien Lp | System and method of determining light source aging |
US8636667B2 (en) * | 2009-07-06 | 2014-01-28 | Nellcor Puritan Bennett Ireland | Systems and methods for processing physiological signals in wavelet space |
US8494786B2 (en) | 2009-07-30 | 2013-07-23 | Covidien Lp | Exponential sampling of red and infrared signals |
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 |
DE112010004682T5 (en) | 2009-12-04 | 2013-03-28 | Masimo Corporation | Calibration for multi-level physiological monitors |
US20120229800A1 (en) * | 2011-03-08 | 2012-09-13 | Fluke Corporation | Pulse oximeter test instruments and methods |
US10541652B2 (en) | 2015-06-27 | 2020-01-21 | Intel Corporation | Apparatus and method for filter settling calibration to improve speed of tracking and cancelling of DC offset |
US10568530B2 (en) | 2015-06-27 | 2020-02-25 | Intel Corporation | Apparatus and method for tracking and cancelling DC offset to acquire small AC signal |
TWI708070B (en) * | 2015-10-22 | 2020-10-21 | 新加坡商海特根微光學公司 | Optical crosstalk calibration for ranging systems |
US10231632B2 (en) | 2016-02-22 | 2019-03-19 | Intel Corporation | Apparatus and method for tracking and cancelling DC offset to acquire small AC signal using dual feedback loops |
CN109157207A (en) * | 2018-08-23 | 2019-01-08 | 深圳北芯生命科技有限公司 | Cross-interference elimination device and method based on FFR measurement |
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2004
- 2004-02-25 US US10/787,541 patent/US7215985B2/en active Active
-
2005
- 2005-02-24 CA CA002556744A patent/CA2556744A1/en not_active Abandoned
- 2005-02-24 JP JP2007500780A patent/JP4701235B2/en not_active Expired - Fee Related
- 2005-02-24 CN CNA2005800058586A patent/CN1937952A/en active Pending
- 2005-02-24 AU AU2005216981A patent/AU2005216981A1/en not_active Abandoned
- 2005-02-24 MX MXPA06009756A patent/MXPA06009756A/en not_active Application Discontinuation
- 2005-02-24 EP EP05731575A patent/EP1722677A1/en not_active Withdrawn
- 2005-02-24 WO PCT/US2005/006316 patent/WO2005082241A1/en active Application Filing
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US4942877A (en) * | 1986-09-05 | 1990-07-24 | Minolta Camera Kabushiki Kaisha | Device for measuring oxygen saturation degree in arterial blood |
US20010002206A1 (en) * | 1997-04-14 | 2001-05-31 | Diab Mohamed K. | Method and apparatus for demodulating signals in a pulse oximetry system |
US5995858A (en) | 1997-11-07 | 1999-11-30 | Datascope Investment Corp. | Pulse oximeter |
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Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP3406194A1 (en) * | 2017-05-23 | 2018-11-28 | Ams Ag | Circuit arrangement for an optical monitoring system and method for optical monitoring |
WO2018215240A1 (en) * | 2017-05-23 | 2018-11-29 | Ams Ag | Circuit arrangement for an optical monitoring system and method for optical monitoring |
US11344234B2 (en) | 2017-05-23 | 2022-05-31 | Ams Ag | Circuit arrangement for an optical monitoring system and method for optical monitoring |
Also Published As
Publication number | Publication date |
---|---|
CA2556744A1 (en) | 2005-09-09 |
JP2007523715A (en) | 2007-08-23 |
JP4701235B2 (en) | 2011-06-15 |
AU2005216981A1 (en) | 2005-09-09 |
US20050187452A1 (en) | 2005-08-25 |
CN1937952A (en) | 2007-03-28 |
EP1722677A1 (en) | 2006-11-22 |
US7215985B2 (en) | 2007-05-08 |
MXPA06009756A (en) | 2007-03-30 |
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