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`US 20080081972Al
`
`(19) United States
`(12) Patent Application Publication (10) Pub. No.: US 2008/0081972 A1
`(43) Pub. Date:
`Apr. 3, 2008
`Del] reezeny
`
`SYMMETRIC LED ARRAY FOR PULSE
`OXIMETRY
`
`Inventor:
`
`Martin P. lkbreezeny. Danville.
`CA (us)
`
`Correspondence Address:
`(Iovidien
`Il’ Counsel - Respiratory & Monitoring Solutions
`60 Middletown Avenue
`North Haven, CT 06473
`
`Assignee:
`
`Nelleor Pu ritan Bennett
`Incorporated
`
`Appl. No;
`
`“541,287
`
`Filed:
`
`Sep. 29, 2006
`
`Pulse Oximeter
`
`There is provided a sensor for pulse oximeler syslems. The
`sensor comprises a first source ofeleclromagnetic radiation
`configured to operate at a first wavelength, in second source
`of electromagnetic radiation configured to operate at a
`second wavelength. and a lhird source of electmmagnetie
`radiation configured lo operate at a third wavelength. 'l'he
`emission spectra of the firsl mid third sources of electro-
`magnetic radiation] overlap :1l
`their half power level or
`greater and correspond to a center wavelength in [he range
`of 650 to 670 nrn.
`
`US. Patent No. 8,929,965
`
`Publication Classification
`
`Int. Cl.
`A613 5/00
`
`(51)
`
`(52)
`
`(5?)
`
`(2006.01)
`
`6001323: 600810
`
`ABSTRACT
`
`001
`
`Apple Inc.
`Apple Inc.
`APL1008
`APL1008
`U.S. Patent No. 8,929,965
`
`FITBIT, Ex. 1008
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`

`

`Patent Application Publication
`
`Apr. 3, 2008 Sheet 1 of4
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`US 2008/0081972 A1
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`FITBIT, Ex. 1008
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`Patent Application Publication
`
`Apr. 3, 2008 Sheet 2 of 4
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`US 2008/0081972 A1
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`'
`
`64
`
`62
`
`65
`
`66
`
`RedLED2
`
`H IRLED
`
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`
`Wavelength (nm)
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`FITBIT, Ex. 1008
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`

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`Patent Appiication Publication
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`Apr. 3, 2008 Sheet 3 of 4
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`US 2008/0081972 A1
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`7"6
`
`004
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`FITBIT, Ex. 1008
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`

`

`005
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`FITBIT, Ex. 1008
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`

`

`directing the optical path through different amounts or types
`of tissue. and by expanding. compressing. or otherwise
`altering tissue near a sensor.
`[0009]
`Pulse oximetry may utilize light sources that emit
`in at least two different or spectral regions. one that emits in
`the red region (typically about 660 run) and one in the near
`infrared region (typically about 890-940 urn]. Typically.
`LEDs are used as light sources and are held in close
`proximity. l.e.. optically coupled. to a tissue location being
`probed. 111 the context of pulse oximetry. optical coupling
`refers to a relationship between the sensor and the patient,
`permitting the sensor to transmit light into the patient's
`blood profused tissue and permitting a portion of the light to
`return to the sensor after passing through or reflecting from
`within the tissue. The quality of the optical coupling of the
`emitters and detectors is related to the amount of light that
`actually enters the patient’s tissue and the portion of the light
`received by the sensor that passes through the patient’s
`blood profitsed tissue. AS described earlier. motion andr'or
`the application of excessive pressure can have the ellect of
`changing the relative optical coupling efficiency of the light
`sources and the detector. Even when two LEDs are mounted
`side by side. motion induced changes in optical eflicieucy
`have resulted in distortions of the photoplethysmographs
`produced by the two Llile. The result of poor coupling.
`therefore. is a decrease in the accuracy of the sensor.
`[0010]
`Ilomogenizing the light sources using optical cott-
`pling devices is one way ofinitigating the eflect of motion-
`indttced changes in optical efficiency on the accuracy of a
`pulse oximeter. Such techniques. however. generally require
`careful optical alignment. tend to be expensive. or reduce the
`optical coupling elliciency into the tissue.
`[0011]
`Seusor-to-scnsor spectral variation of light sources
`used for oximcter sensors may also affect a pulse oxirneter‘s
`accuracy. Because hemoglobin (l—lel2 and Hl-lb) spectra
`vary more rapidly as a function of wavelength at approxi-
`mately 660 mn than at approximately 940 nm. the precise
`spectral content of the 660 nm light source is more critical.
`Current manufacturing processes used to produce 660 um
`LliDs result
`in a wide distribution of spectral content.
`potentially necessitating modification of the calibration
`model according to actual spectral content of the 660 nm
`source. thus adding cost to the system. Altematively, choos-
`ing only LEDs that emit
`in a narrow wavelength range
`would result in low production yields and higher sensor cost.
`Thus. costs are incurred either by limiting the range of
`wavelengths to reduce the need for calibration. or by allow-
`ing for a wider spectral content and inseniug calibration
`models.
`
`006
`
`SUMMARY
`
`[0012] Certain aspects commensurate in scope with the
`originally claimed invention are set forth below. It should be
`understood that these aspects are presented merely to pro—
`vide the reader with a brief summary of certain forms the
`invention might take and, these aspects are not intended to
`limit the scope of the invention. Indeed. the invention may
`encompass a variety of aspects that may not be set forth
`below.
`In accordance with one aspect of the present inven-
`[0013]
`tion a sensor for pulse oximeter systems is provided. The
`sensor comprises a first source of electromagnetic radiation
`configured to operate at a first wavelength. a second source
`of electromagnetic radiation configured to operate at a
`
`006
`
`US 2008f0081972 A1
`
`Apr. 3, 2008
`
`SYMMETRIC LED ARRAY FOR PULSE
`OXIMETRY
`
`BACKGROUND
`
`1. Field of Invention
`[0001]
`[0002] The present invention relates generally to medical
`devices and. more particularly. to sensors used for sensing
`physiological parameters of a patient.
`[0003]
`2. Description of the Related Art
`[0004] This section is intended to introduce the reader to
`various aspects ol'an that may be related to various aspects
`ot'the present invention. which are described andfor claimed
`below. This discussion is believed to be helpful in providing
`the reader with background information to facilitate a better
`understanding of the various aspects of the present inven-
`tion. Accordingly. it should be understood that these state-
`ments are to be raid in tltis light. and not as admissions of
`prior art.
`I11 the field oi" medicine. doctors ofien desire to
`[0005]
`certain physiological
`characteristics of
`their
`monitor
`patients. Accordingly. a wide variety of devices have been
`developed for monitoring many such characteristics of a
`patient. Such devices provide doctors and other ltealthcare
`personnel with the information they need to provide the best
`possible healthcare for their patients. As a result. such
`monitoring devices have become an indispensable part of
`modern medicine.
`
`[0006] One technique for tnonitoring certain physiological
`characteristics of a patient is commonly referred to as pulse
`oximetry. and the devices built based upon pulse oximetry
`techniques are commonly referred to as pulse oximcters.
`Pulse oximctry may be used to measure various blood flow
`characteristics, such as the blood oxygen saturation of
`hemoglobin in arterial blood. the volume ot'individual blood
`pulsations supplying the tissue. andJor the rate of blood
`pulsations corresponding to each heart beat ot‘a patient. In
`fact, the “pulse” in pulse oximetry refers to the time varying
`amount of arterial blood in the tissue during each cardiac
`cycle.
`Pulse oximeters typically utilize a non-invasive
`[0007]
`sensor that transmits or reflects electromagnetic radiation.
`such as light. through a patient’s tissue and that photoelec-
`trically detects the absorption and scattering of the trans-
`mitted or reflected light in such tissue. One or more of the
`above physiological characteristics may then be calculated
`based upon the amount of light absorbed and scattered. More
`specifically, the light passed through or reflected from the
`tissue is typically selected to be of one or more wavelengths
`that may be absorbed and scattered by the blood in an
`amount correlative to the amount of blood constituent
`present in the tissue. The measured amount of light absorbed
`and scattered may then be used to estimate the amount of
`blood constituent in the tissue using various algoritluns.
`[0008] Certain events can create error in these measure-
`ments. l-‘or example. pulse oximetry measurements may be
`sensitive to movement of the sensor relative to the patient‘s
`tissue, and various types of motion may cause artifacts that
`may obscure the blood constituent signal. Specifically.
`motion artifacts may be caused by moving a sensor in
`relation to the tissue. increasing or decreasing the physical
`distance between emitters and detectors in a sensor, chang-
`ing the angles ofincidents and interfaces probed by the light.
`
`FITBIT, Ex. 1008
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`

`US 2008f0081972 A1
`
`Apr. 3, 2008
`
`It should be appreciated that in the development of any such
`actual
`implementation. as in any engineering or design
`project. numerous implementatiotnspecific decisions must
`be made to achieve developer‘s specific goals, such as
`compliance with system-related and business-related con-
`straints. which may vary from one implementation to
`another. Moreover.
`it should be appreciated that such a
`development effort might be complex and time consuming.
`but would nevertheless be a routine undertaking of design.
`fabrication. and manufacture for those of ordinary skill
`having the benefit of this disclosure.
`[0024]
`In accordance with aspects of the present inven-
`tion. techniques are disclosed for reducing the susceptibility
`of pulse oximeters to error caused by motion or spectral
`variation of light sources. Additionally. techniques are dis-
`closed that allow for the operation ofpulse oximetry systems
`with a broad spectral content and. potentially, without cali~
`bration.
`
`second wavelength and a third source of electromagnetic
`radiation configured to operate at a third wavelength. The
`first and third sources of electromagnetic radiation overlap at
`their half power level or greater and correspond to a center
`wavelength in the range of 650 to 670 nm. A photodetector
`is configured to receive electromagnetic radiation from
`blood-perfused tissue irradiated by the first. second and third
`sources of electromagnetic radiation.
`[0014]
`In accordance with another aspect of the present
`invention there is provided a sensor comprising a first source
`of electromagnetic radiation configured to operate at a first
`wavelength. 3 second source of electromagnetic radiation
`configured to operate at a second wavelength and a third
`source of electromagnetic radiation configured to operate at
`a third wavelength. A photodetector is configured to receive
`electromagnetic radiation from the blood-perfused tissue.
`and the first and thjrd sources of electromagnetic radiation
`are symmetrically disposed spatially relative to the photo-
`detector.
`in accordance with yet another aspect of the
`[0015]
`present invention a sensor comprising a first light emining
`diode configured to emit
`radiation having a maximum
`intensity corresponding to wavelengths in a red region of the
`electromagnetic spectrum. The sensor also comprises a
`second LEI) configured to operate in the near-infrared
`region of the electromagnetic spectrtun and a third LED
`configured to operate in the red region of the electromag-
`netic spectrum. The third LED has a maximum intensity at
`a wavelength greater than 650 um and greater than the
`wavelength at which the first LED has a maximum. The first
`LED and third LED are spectrally symmetrical with respect
`to a center wavelength in the range 650 to 670 mu.
`
`BRIEF DESCRIPTION OF THE DRAWINGS
`
`007
`
`[0025] Turning to FIG. 1. a block diagram of a pulse
`oximeter system in accordmtce with an exemplary embodi—
`ment of the present invention is illustrated and generally
`designated by the reference numeral 10. The pulse oximeter
`system 10 includes a sensor 11 having a detector 12 which
`receives electromagnetic radiation from the blood perfused
`tissue of a patient 14. The electromagnetic radiation origi—
`nates from emitters 16. A photoelectric current is generated
`when the electromagnetic radiation scattered and absorbed
`by the tissue arrives at the detector 12. The current signal
`produced by the detector 12 is amplified by an amplifier 18
`prior to being sent to the pulse oximeter 20.
`[0026] The emitters 16 may be one or more LEDs con—
`figured to emit in the red and near infrared regions of the
`electnimagnetic specu'tun. As will be explained in greater
`detail below.
`the emitters 16 may be oriented to provide
`spatial symmetry about an axis. Additionally, the emitters 16
`may be spectrally sytmnetrical about a central wavelength to
`eliminate the use of a spectrum calibration model.
`[0027]
`In addition to providing a signal corresponding to
`the amount of electromagnetic radiation scattered and
`absorbed by the tissue. the sensor 11 may also be configured
`to provide calibration data to the pulse oximeter 20 via an
`encoder 21. Pulse oximetry algorithms typically use coetli-
`cients indicative ofcertain parameters ol'a particular system.
`The particular set of coeliicients chosen for a particular set
`of wavelength spectra is determined by the value indicated
`by encoder 21 corresponding to a particular light source in
`a particular sensor. In one configuration. multiple resistor
`values may be assigned to select different sets 01‘ coelli-
`ciems.
`in this instance. the encoder 21 may include one or
`a plurality of resistor values and a detector 22 located in the
`pulse oximeter 20 reads the resistor values and selects
`coeflieients From a stored table. Alternatively. the encoder 21
`may be a memory that either stores the wavelength infor-
`mation or the coeflicients. Thus. the encoder 21 and the
`decoder 22 allow the pulse oximetcr 20 to be calibrated
`according to the particular wavelengths of the emitters 16.
`[0028]
`In an exemplary embodiment. the pulse oximeter
`20 includes a tnicroprocessor 24 that processes data received
`from the sensor 11 to compute various physiological param-
`eters. The pulse oximeter 20 may also include a random
`access memory (RAM) 26 for storing data and an output
`display 28 for displaying computed parameters. A time
`processing unit (’I‘PU) 30 may be provided to control the
`timing of the pulse oximeter 20. The TPU may be coupled
`
`[0016] Advantages of the invention may become apparent
`upon reading the following detailed description and upon
`reference to the drawings. in which:
`[0017]
`FIG.
`1
`illustrates a block diagram of a pulse
`oximeter system in accordance with an exemplary embodi-
`ment of the present invention:
`[0018]
`FIG. 2 illustrates spatial symmetry of the light
`sources in accordance with em exemplary embodiment of the
`present invention:
`[0019]
`FIG. 3 illustrates an emission intensity plot of an
`emitter in accordance with an embodiment of the present
`invention:
`[0020]
`FIG. 4 illustrates the emission intensity plots of
`two emitters spectrally symmetrical relative to a central
`wavelength in accordance with embodiments of the present
`invention:
`[0021]
`FIG. 5 illustrates an electrical cotfligtuation for
`LEDS of a pulse oximeter in accordance with an exemplary
`embodiment of the present invention; and
`[0022]
`FIG. 6 illustrates a cross—sectional view ofa pulse
`oximeter sensor in accordance with an exemplary embodi—
`ment of the present invention
`
`DETAILED DESCRIPTION OF SPECIFIC
`[EMBODIMENTS
`
`[0023] One or more specific embodiments of the present
`invention will be described below. In an elfort to provide a
`concise description ofthese embodiments. not all features of
`an actual implementation are described in the specification.
`
`007
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`FITBIT, Ex. 1008
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`

`above. FIG. 3 illustrates the emission intensity plot of an
`exemplary light emitter relative to the wavelength. Specifi-
`cally. FIG. 3 illustrates that the emitter exhibits an emission
`intensity maximmn at a center wavelength he. The wave-
`lengths it“ and 166 of the Milk. 64 and 66 are shown
`symmetrically disposed about the center wavelength hr. To
`provide spectral symmetry. two emitters are used that have
`emission intensity maxima at wavelengths equidistant in
`nanometers from the central wavelength AL. and on opposite
`spectral sides of the central wavelength L. which may be
`selected to be 660 nm. for example. Specifically. the two
`wavelengths A54 and it“. are selected to havo nlaxima at
`wavelengths that overlap at their half power level or greater
`at the center wavelength ht. such that when summed together
`they achieve a maximum intensity at the center wavelength
`kc, where the maximum intensity is greater than that of
`either LED 64 or LED 66 alone. For example. if the spectral
`bandwidth of the wavelengths hf. in“ and it“ are the same.
`two wavelengths 154 and it“, may be selected to correspond
`to the half power level or greater of the center wavelength
`kc. In other words. if the LED 64 has a maximum at 650 um
`and the LED 66 has a maximum at
`(:70 nm and the
`respective signals have not decreased beyond their half
`power level (—3 dB) at 660 nm. then the additive maximum
`of the LEI) 64 and LED 66 will occur at 660 nm. Thus. a
`stronger signal at the center wavelength. such as 660 um
`may be achieved through spectral symmetry techniques.
`[0034] Additionally.
`the use of spectral symmetry may
`eliminate the need for a calibration model. The hemoglobin
`(I-lbO2 and l-II-lh] spectra vary more rapidly as a Function of
`wavelength at 660 not than at 940 nm. Therefore. the precise
`spectral content of the red light source is more critical than
`that of the NIRJ'IR light source. Accurate predictions of
`oxygen saturation may be achieved by modification of the
`calibration model according to the spectral content of the
`particular red light sources being used. as discussed above.
`Spectral symmetry techniques. however. may be used to
`obviate calibration.
`
`008
`
`[0035] Referrng to FIG. 4. the emission intensity of the
`two LEDs 64 and 66 having maxima at wavelengths A54 and
`it“. which are symmetrical about the center wavelength Ac,
`e.g.. approximately 660 nm. are illustrated. A maximan at
`the center wavelength.
`indicated by the dashed line 67.
`occurs due to the additive etibcts ot‘ the I,.F,Ds 64 and 66
`emitting at the spoctrally symmetrical wavelengths A54 and
`7.56 which overlap at their half power level or greater. As
`discussed above. even though the LEDs 64 and 66 are not
`operating at the center wavelength he, they may combine to
`create a maximum at the center wavelength la. 'Ihus. the
`technique of spectral symmetry may eliminate the wave—
`length speciiic calibration because the LEDs 64 and 66 are
`selected to be summed to create a maximum at the center
`wavelength It: for which the pulse oximeter may already be
`programmed. It is inherent in this technique that the wave—
`length maximum, and not the spectral width of the light
`source, is used for the calibration of oximeter sensor light
`sources.
`
`Furthermore. because the light sources are spec—
`[0036]
`trally symmetrical and their intensities may add to have a
`maximum at the center wavelength hr. a wider range of light
`source spectra may be used. For example the range of
`currently allowed wavelengths for the 660 nm LEDs is
`approximately 650 nm to 670 nm. According to the tech-
`niques presenth herein. however. it may be possible to use
`
`008
`
`US 2008f0081972 A1
`
`Apr. 3, 2008
`
`to light drive circuitry 32 and a switch 34. The light drive
`circuitry 32 controls light emissions of the emitters l6. and
`the switch 34 receives and controls the gating—in of the
`amplified signals from the detector 12. The received signals
`are passed from the switch 34 through a second amplifier36.
`a filter 38. and an analogAto—digital converter (AID) 40.
`beliore arriving at the microprocessor 24.
`[0029] Upon receiving the signals. the microprocessor 24
`calculates the oxygen saturation and other physiological
`parameters. In calculating the physiological parameters. the
`microprocessor 24 uses algorithms stored on a read-only
`memory (ROM) 44 and data stored in the RAM 26. As
`discussed above. the algorithms typically use coellicients
`which correspond to the wavelengths of light used and
`calibrate the pulse oxitneter 20 to the panicular wavelengths
`being used.
`Implementation of spectral symmetry tech—
`niques may. however. eliminate such calibration.
`[0030] The display 28 outputs the physiological param—
`eters. such as oxygen saturation. calculated by the pulse
`oximetcr 20. “the block diagram of the pulse oximetcr
`system It] is exemplary. and it should be understood that
`various alternative configurations may be possible. For
`example. there may be multiple parallel paths of separate
`amplifiers, filters. and AID converters for multiple light
`wavelengths or spectra received. Additionally. implementa—
`tion of spectral symmetry techniques may obviate the
`encoder 21 and decoder 22.
`
`Spatial symmetry of the emitters 16 may provide a
`[0031]
`level of immunity against motion induced artifacts. FIG. 2
`diagrammatically illustrates the emitter portion of a sensor
`having emitter LEDs 64. 65 and 66 symmetrically oriented
`relative to an axis 62 in accordance with an exemplary
`embodiment of the present invention. The first 1.1.51) 64 is
`positioned on one side of the center Hit) 65. while the
`second LED 66 is positioned on the other side of the center
`LED 65. The axis 62 runs through the center of the center
`LED 65 and may represent the long axis ofa patient's linger
`to which the LEDs may couple. The center LED 65 typically
`emits radiation in the infrared (IR) or near infrared (NMR)
`range, While the [.ISDS 64 and 66 have similar spectral
`outputs in the red range of approximately 600 to 800 nm to
`help ensure that any coupling issues that may occur due to
`movement of tissue relative to one LED may be compen—
`sated t‘or by the other LED. For example. if the finger moves
`away from the LED 64. resulting in poor coupling with LED
`64. the coupling of the finger with LED 66 may still exhibit
`good coupling or even improved coupling due to the move—
`ntcnt.
`
`[0032] As discussed above. pulse oximeters typically
`employ light sources that operate in the near infrared (N1th
`infrared {IR} and the red range of the electromagnetic
`spectrum. The dill'erent wavelengths ot‘ light generate dif-
`ferent levels of current in the photodeteetor 12. As the red
`range produces a lower photocurrent in the photodetector
`12. I..l.il)s that emit in this range may be selected as the [.5le
`64 and 66. Because the signal from the twu I.l.il)s 64 and 66
`is additive. the signal-to-noise ratio of the sensor may be
`increased. thus. providing better readings.
`[0033]
`In addition to the LEDS 64 and 66 being physically
`disposed in a symmetrical relationship. or in the alternative.
`the wavelengths of the LEDs 64 and 66 may be spectrally
`symmetrical with respect to one another. Spectral symmetry
`of the 115135 64 and 66 may be implemented in combination
`with or independent from the spatial symmetry described
`
`FITBIT, Ex. 1008
`
`

`

`US 2008f0081972 Al
`
`Apr. 3, 2008
`
`Specifically. the sensor 68 includes a curved shape about the
`patient‘s tissue 14 which permits rocking movement accord-
`ing to the cttrved shape of the housing 70. but which limits
`other movement. Movement such as rocking along the
`curvature of the housing 70 may be anti-correlated by the
`spatial symmetry of the sensor 68. thus reducing motion"
`induced artifacts.
`
`009
`
`[0040] As stated above. spatial symmetry techniques may
`be used in combination with or independent of the spectral
`symmetry technique. When implemented in a system that
`does not have spectral symmetry.
`it may be desirable to
`calibrate the pulse oxintetcr. When spectral symmetry tech-
`niques are implemented. the calibration may be unnecessary.
`as described above. In the event that spectral symmetry is
`implemented and the its is ttot 660 nm,
`it may still be
`desirable to calibrate according to the particular hr.
`[004]]
`Several advantages are achieved by implementing
`the techniques described herein. For example. spatial syms
`metry may provide anti-correlation 01‘ motion-induced arti-
`facts and increase the signal-to-noise ratio. Motion-induced
`artifacts are typically a result ofchanges in the coupling of
`the sensor with the patient's tissue. The spatial symmetry
`anti-correlates the tttotiott irtdttced artifacts by providing two
`LEDs symmetrically disposed about an axis of movement
`such that as the patient‘s tissue moves away from one LED
`the tissue couples with another l.l.i[) operating at the same
`wavelength. Additionally. the summed signal from the sym—
`metrically disposod LliDs may provide a stronger signal
`than a single LED to improve the signal—lo—noise ratio for
`wavelengths which have a weaker photodetection effect.
`[0042] The implementation of spectral symmetry may also
`provide a stronger signal at wavelengths which have a
`weaker photo detection efi'ect. The combined emission
`strength of the tvvo LliDs spectrally oriented about a central
`wavelength may provide a stronger signal for detection if
`each of LEDs have etttission wavelettgtlts which overlap
`above their half power level. as described above with
`reference to FIG. 4. Furthermore. the spectral symmetry
`allows the use of LEDs having a wider range of spectral
`content. Selecting light sources having maxima symmetri—
`cally diSposod about a center wavelength in the range of 650
`to 670 um allows for is summed signal with a maximum
`witltin the 650 to 67'0 nrtt range. Thus. LEDs emitting
`outside of the 650 to 670 ttm range may be used when paired
`with an LED having a peak emission wavelength symmetri—
`cally disposed about the center wavelength. as long as the
`spectra of the LEDs overlap at the center wavelength at their
`respective half power levels or greater.
`[0043]
`Implementation of spectra] synunetry may also
`allow for calibmtion-free sensors. Assuming that the wave-
`length maximum and not the spectral width of the LEDs is
`the most important aspect ofthe calibration. a cettter wave—
`length can be selected about which LED pairings are spec—
`trally symmetrical. The pulse oximeter 20 can be set to
`operate according to a center wavelength. i.e. according to
`coefficients. associated with the center wavelength. and no
`calibration is required. If variable spectral width due to the
`use of two LEDs is found to limit
`the accuracy of the
`measurement. an optical coating could be applied either to
`the light source or detector to limit the spectral width. For
`example. the detector could be coated with a material that
`passes light only with bands around 660 and 890 nm. but
`blocks the detection of light in all other spectral regions. In
`this way. the detected spectral band width would be prima-
`
`LEDs emitting outside the range of wavelengths between
`650 and 670 not. For exampIe. a first LED can be selected
`to have an emission peak at a wavelength less than 670 pm.
`such as 648 run. and second LLiD utay be selected to have
`an emission peak at a wavelength greater than 650 thI. such
`as 672 run. As long as signals from the first and second LEDs
`overlap at half power (—3 dB) or greater. :1 peak will be
`created by the overlap. Assuming that each LED has an
`equivalent spectral bandwidth. there will be a peak at 660
`turn. Alternatively. the first LED can be selected to etnit at
`640 not and the second LIED can be selected to emit at 660
`nm. thus providing spectra] symmetry at 650 nm. Again. as
`long as the signals emitted from the first and second LEDs
`overlap at hall" power or greater at 650 um. there will be a
`peak at 650 11m. The use of LEDs producing inaximas at
`wavelength other than 660 um. however, ntay require a
`calibration model to compensate for the lack ol'absorbance
`of hemoglobin at that particular wavelength. Additionally,
`the actual range of wavelengths that may be implemented
`may be limited by several factors.
`including the spectral
`bandwidth ol'the particular LEDs. the pltotoseusitivity of the
`detector and litnits on the spectrophotographic response of
`hemoglobin at wavelengths other than 66011111. Specifically.
`it the LEDs only have a spectral bandwidth of twenty
`nanometers. the spectrally symmetrical LEEDS can only have
`peaks twenty nanometers or less apart (i.e. ten nanometers
`from a desired center wavelength
`the
`[0037]
`In an alternative exemplary embodiment.
`implementation oi" the spectra] symmetry techniques may
`produce a peak having a broader spectra] bandwidth. rather
`than increasing the magnitude of the signal at the center
`wavelength. Specifically, the peak generated by summing
`the emitted wavelengths may not necessarily be greater than
`the peak generated by the individual Ltle 64 and 66
`themselves. For example. the summed peak may have a
`magttitttde approximately equivalent
`to the magnitude of
`peaks generated by the [..EDs 64 and 66 alone. Accordingly.
`the intensity of the emissions across the spectra will be
`relatively flat between the wavelengths being used and at the
`center anclength. The combined signal would provide a
`broader spectral bandwidth a the center wavelength. as the
`bandwidth extends from hall'power level on the blue side of
`the signal from LED 64 to the half power level on the red
`side of the LED 66.
`
`[0038] An exemplary schematic of the electrical contigu-
`ratiott of the multiple LED; is illustrated in FIG. 5. The
`configuration of the LEDs may be the same regardless of
`whether the emitters provide spectral and/or spatial symme-
`try. The two [.l:i[)s 64 and 66 are electrically configured to
`emit
`light coincidentally. whereas the center LED 65 is
`configured to emit light while the LEDs 64 and 66 are oll'.
`[0039] Taming to FIG. 6. a cross sectional view of a
`settsor in accordance with an exemplary embodiment of the
`present invention is illustrated and generally designated by
`the reference numeral 68. The cross sectional view of the
`sensor 68 shows a plurality of l.l-il')s 64. 65 and 66 oriented
`about an axis 62. The center LED 65 and the detector 16 are
`
`bisected by the axis 62. The LEDS 64. 65. and 66 transmit
`electrotttagnetic radiation through a patient‘s tissue 14
`which is detected by the detector 16. The housing 70 of the
`pulse oximeter 68 may be designed to limit moventent of the
`patient 14 relative to the LEDs 64. 65. 66 and the detector
`16. thus. reducng artifacts due to motion and poor coupling
`of the LEDs 64, 65. 66 and detector 16 to the patient.
`
`009
`
`FITBIT, Ex. 1008
`
`

`

`US 2008f0081972 A1
`
`Apr. 3, 2008
`
`electrical ctlrrent.
`
`8. The sensor of claim 7. wherein the material comprises
`a multilayer dielectric film.
`9. The sensor of claim 7. wherein the material comprises
`a light-absorbing dye.
`least one ol‘ the
`It). The sensor of claim I. wherein at
`sources is coated with a material that limits the spectral
`bandwidth emitted light.
`1], The sensor of claim 10. wherein the material com-
`prises a multilayer dielectric film.
`12. The sensor of claim 10. wherein the material com-
`prises a light-absorbing dye.
`13. A system for determining physiological parameters
`comprising:
`a sensor comprising:
`a first light entitling diode (LED) configured to emit
`radiation in the red region of the electromagnetic
`spectrtun. the first LED having a maximum wave-
`length less than 670 nm:
`a second l.l.il) configured to operate in the near-infrared
`region of the electromagnetic spectrum:
`a third LED configured to operate in the red region of
`the electromagnetic spectrum. the third LED having
`a tnaxinntm wavelength greater than 650 nm. the
`third LED having a maximum wavelength greater
`than the first [Jill wherein the first LED and third
`Mil) are spectrally symmetrical with respect to a
`center wavelength in the range 650 to 670 nm: and
`a photodetector configured to generate a signal corre-
`sponding to received electromagnetic radiation from
`blood-perfused tissue irradiated by the first. second
`and third sources of electromagnetic radiation; and
`a pulse oximeter configured to compute physiological
`parameters based on the signals generated by the pho-
`todetector.
`14. The system of claitn 13. wherein the first LED and
`third LED are spatially oriented symmetrically about an axis
`relative to the second LED.
`15. The system ofclaim 14. wherein the sensor comprises
`a curved surface Configured to allow optical coupling of a
`patient’s finger with the first. second and third LIEDs. and the
`photodetcctor.
`16. The systetn of claim 15. wherein the cttrved surface
`inhibits axial movement of the patient‘s finger.
`17. A method for detemiining physiological parameters
`rising a pulse oxitneter comprising:
`light
`transmitting electromagnetic radiation from a first
`emitting diode [LED]. 3 second LED and a third [.1111
`wherein the first