|Número de publicación||US20060195026 A1|
|Tipo de publicación||Solicitud|
|Número de solicitud||US 11/407,776|
|Fecha de publicación||31 Ago 2006|
|Fecha de presentación||19 Abr 2006|
|Fecha de prioridad||1 Abr 1994|
|También publicado como||US6662033, US7349726, US7376454, US7415298, US20020082489, US20040204639, US20060189862, US20060195027, US20060211929, US20070156039|
|Número de publicación||11407776, 407776, US 2006/0195026 A1, US 2006/195026 A1, US 20060195026 A1, US 20060195026A1, US 2006195026 A1, US 2006195026A1, US-A1-20060195026, US-A1-2006195026, US2006/0195026A1, US2006/195026A1, US20060195026 A1, US20060195026A1, US2006195026 A1, US2006195026A1|
|Inventores||James Casciani, Paul Mannheimer, Steve Nierlich, Stephen Ruskewicz|
|Cesionario original||Casciani James R, Mannheimer Paul D, Nierlich Steve L, Ruskewicz Stephen J|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citada por (22), Clasificaciones (10)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
This application is a continuation of U.S. application Ser. No. 10/698,962, filed Oct. 30, 2003, which is a continuation of U.S. application Ser. No. 09/882,371, filed Jun. 14, 2001, now U.S. Pat. No. 6,662,033, which is a continuation of U.S. application Ser. No. 09/003,413, filed Jan. 6, 1998, now U.S. Pat. No. 6,272,363, which is a continuation of U.S. application Ser. No. 08/413,578, filed Mar. 30, 1995, now U.S. Pat. No. 5,782,237, which is a continuation-in-part of U.S. application Ser. No. 08/221,911, filed Apr. 1, 1994, now U.S. Pat. No. 5,421,329, the disclosures of which are incorporated herein by reference.
Pulse oximetry is used to continuously monitor the arterial blood oxygen saturation of adults, pediatrics and neonates in the operating room, recovery room, intensive care units, and increasingly on the general floor. A need exists for pulse oximetry in the delivery room for monitoring the oxygen status of a fetus during labor and delivery, and for monitoring the oxygen status of cardiac patients.
Pulse oximetry has traditionally been used on patient populations where arterial blood oxygen saturation is typically greater than 90%, i.e., more than 90% of the functional hemoglobin in the arterial blood is oxyhemoglobin and less than 10% is reduced hemoglobin. Oxygen saturation in this patient population rarely drops below 70%. When it does drop to such a low value, an unhealthy clinical condition is indicated, and intervention is generally called for. In this situation, a high degree of accuracy in the estimate of saturation is not clinically relevant, as much as is the trend over time.
Conventional two wavelength pulse oximeters emit light from two Light Emitting Diodes (LEDs) into a pulsatile tissue bed and collect the transmitted light with a photodiode positioned on an opposite surface (transmission pulse oximetry), or an adjacent surface (reflectance pulse oximetry). The LEDs and photodetector are housed in a reusable or disposable sensor which connects to the pulse oximeter electronics and display unit. The “pulse” in pulse oximetry comes from the time varying amount of arterial blood in the tissue during the cardiac cycle, and the processed signals from the photodetector create the familiar plethysmographic waveform due to the cycling light attenuation. For estimating oxygen saturation, at least one of the two LEDs' primary wavelength must be chosen at some point in the electromagnetic spectrum where the absorption of oxyhemoglobin (HbO2) differs from the absorption of reduced hemoglobin (Hb). The second of the two LEDs' wavelength must be at a different point in the spectrum where, additionally, the absorption differences between Hb and HbO2 are different from those at the first wavelength. Commercial pulse oximeters utilize one wavelength in the near red part of the visible spectrum near 660 nanometers (nm), and one in the near infrared part of the spectrum in the range of 880-940 nm (See
Photocurrents generated within the photodetector are detected and processed for measuring the modulation ratio of the red to infrared signals. This modulation ratio has been observed to correlate well to arterial oxygen saturation as shown in
The choice of emitter wavelengths used in conventional pulse oximeters is based on several factors including, but not limited to, optimum signal transmission through blood perfused tissues, sensitivity to changes in arterial blood oxygen saturation, and the intensity and availability of commercial LEDs at the desired wavelengths. Traditionally, one of the two wavelengths is chosen from a region of the absorption spectra (
According to exemplary embodiments of the invention, more accurate estimates of low arterial oxygen saturation using pulse oximetry are achieved by optimizing a wavelength spectrum of first and second light sources so that the saturation estimates at low saturation values are improved while the saturation estimates at high saturation values are minimally adversely affected as compared to using conventional first and second wavelength spectrums. It has been discovered that calculations at low saturation can be significantly improved if the anticipated or predicted rates of absorption and scattering of the first wavelength spectrum is brought closer to, optimally equal to, the anticipated or predicted rates of absorption and scattering of the second wavelength spectrum than otherwise exists when conventional wavelength spectrum pairs are chosen, such as when conventionally using a first wavelength centered near 660 nm and a second wavelength centered anywhere in the range of 880nm-940 nm.
The present techniques solve a long felt need for a pulse oximeter sensor and system which provides more accurate estimates of arterial oxygen saturation at low oxygen saturations, i.e. saturations equal to or less than 80%, 75%, 70%, 65%, or 60%, than has heretofore existed in the prior art. The sensor and system is particularly useful for estimating arterial saturation of a living fetus during labor where the saturation range of principal importance and interest is generally between 15% and 65%, and is particularly useful for estimating arterial saturation of living cardiac patients who experience significant shunting of venous blood into their arteries in their hearts and hence whose saturation range of principle importance and interest is roughly between 50% and 80%. By contrast, a typical healthy human has a saturation greater than 90%. The invention has utility whenever the saturation range of interest of a living subject, either human or animal, is low.
In addition to providing better estimates of arterial oxygen saturation at low saturations, the sensor, monitor, and system disclosed herein may provide better and more accurate oxygen saturation estimates when perturbation induced artifacts exist and are associated with the subject being monitored.
When the rates of absorption and scattering by the tissue being probed by the first and second wavelength spectrums are brought closer together for the saturation values of particular interest, improved correspondence and matching of the tissue actually being probed by the first and second wavelengths is achieved, thus drastically reducing errors introduced due to perturbation induced artifacts. For example, when light of one wavelength is absorbed at a rate significantly higher than that of the other wavelength, the light of the other wavelength penetrates significantly further into the tissue. When the tissue being probed is particularly in-homogenous, this difference in penetrations can have a significant adverse impact on the accuracy of the arterial oxygen saturation estimate.
Perturbation induced artifacts include, but are not limited to, any artifact that has a measurable impact on the relative optical properties of the medium being probed. Perturbation induced artifacts include but are not limited to the following:
In one embodiment, there is provided a fetal pulse oximeter sensor with a light source optimized for the fetal oxygen saturation range and for maximizing the immunity to perturbation induced artifact. A far red and an infrared light source may be used, with the far red light source having a mean wavelength between 700-790 nm. The infrared light source can have a mean wavelength as in prior art devices used on patients with high saturation, i.e., between 800-1000 nm. As used herein, “high saturation” shall mean an arterial oxygen saturation greater than 70%, preferably greater than 75%, alternatively greater than 80%, optionally greater than 90%.
The fetal sensor may be optimized by arranging the spacing between the location the emitted light enters the tissue and the location the detected light exits the tissue to minimize the sensitivity to perturbation induced artifact.
According to one embodiment, electrooptic transducers (e.g., LEDs and photodetectors) are located adjacent to the tissue where the light enters and exits the tissue. According to an alternate embodiment, the optoelectric transducers are located remote from the tissue, for example in the oximeter monitor, and optical fibers interconnect the transducers and the tissue with the tissue being illuminated from an end of a fiber, and light scattered by the tissue being collected by an end of a fiber. Multiple fibers or fiber bundles are preferred.
The typical oxygen saturation value for a fetus is in the range of 5-65%, commonly 15-65%, compared to the 90% and above for a typical patient with normal (high) saturation. In addition, a fetal sensor is subject to increased perturbation induced artifact. Another unique factor in fetal oximetry is that the sensor is typically inserted through the vagina and the precise location where it lands is not known in advance.
All of these features one unique to fetal oximetry or oximetry for low saturation patients and provide a sensor which optimizes the immunity to perturbation induced artifacts. This optimization is done with a trade-off on the sensitivity to changes in saturation value. This trade-off results in a more reliable calculation that is not obvious to those who practice the prior art methods which attempt to maximize the sensitivity to changes in the saturation value. The improvement in performance that results from these optimizations are applicable to both reflectance and transmission pulse oximetry. An example of a fetal transmission pulse oximetry configuration usable with the present invention is described in U.S. patent application Ser. No. 07/752,168, assigned to the assignee of the present invention, the disclosure of which is incorporated herein by reference. An example of a non-fetal transmission pulse oximetry configuration usable with the present invention is described in U.S. Pat. No. 4,830,014, assigned to the assignee of the present invention, the disclosure of which is incorporated herein by reference.
FIGS. 26A-B are diagrams of a single package, dual emitter package used in an exemplary embodiment of the present invention; and
An understanding of the design of the fetal sensor disclosed herein benefits from an understanding of the environment in which the sensor will operate.
The general paths of light from an emitter 20 to a photodetector 22 are illustrated by arrows 24 and 26. Arrow 24 shows light which passes almost directly from emitter 20 to detector 22, basically shunted from one to the other, passing through very little blood perfused tissue. Arrow 26, on the other hand, illustrates the deeper penetration of another path of the light. The depth of penetration is affected by the wavelength of the light and the saturation. At low saturation, infrared light penetrates deeper than near red, for instance. The deeper penetration can result in an undesirable variation between the infrared and red signals, since the IR signal will pass through more different layers.
Also illustrated in
The second type of perturbation mentioned in the summary is variations in the concentration of blood in the tissue from patient to patient or over time. A lower concentration results in less absorption, increasing the penetration depth. The inventors estimate that the mean penetration depth of photons in a medium is related to the product of the absorption and scattering coefficients, and this estimate is consistent with the findings of Weiss et al., “Statistics of Penetration Depth of Photons Re-emitted from Irradiated Tissue”, Journal of Modern Optics, 1989, Vol. 36, No. 3, 349-359, 354, the disclosure of which is incorporated herein by reference.
Absorption of light in tissue in the visible and near infrared region of the electromagnetic spectrum is dominated by the absorption characteristics of hemoglobin. Absorption coefficients of hemoglobin can be found in the literature, for example Zijlstra et al., “Absorption spectra of human fetal and adult oxyhemoglobin, de-oxyhemoglobin, carboxyhemoglobin and methemoglobin”, Clinical Chemistry, 37/9, 1633 -1638, 1991 (incorporated herein by reference). Measured scattering coefficients of tissue are influenced by the methodology of measurement and the model used to fit the data, although there is general agreement in the relative sensitivity to wavelength regardless of method. Tissue scattering coefficients used by the inventors are based on diffusion theory, and are taken from Schmitt, “Simple photon diffusion analysis of the effects of multiple scattering on pulse oximetry”, IEEE Transactions on Biomedical Engineering, Vol. 38, No. 12, December 1991, the disclosure of which is incorporated herein by reference.
For low tissue oxygen saturation, points C and D on curve 102 graphically indicate that there is a very significant mismatch between the product of the absorption and scattering coefficients of the 660 nm near red and 892 nm infrared light, with the near red light being more strongly absorbed and scattered. This very significant absorption and scattering mismatch results in very different tissue being probed by the near red and infrared light which significantly degrades the accuracy of the arterial oxygen saturation calculation. In addition, when a large range of low arterial oxygen saturations need to be accurately calculated, as when monitoring a fetus during labor where the range of arterial oxygen saturations can extend between 15% and 65%, it is evident from
On the other hand, points D and E on curve 102 in
One embodiment optimizes the wavelengths used for a sensor to estimate fetal arterial oxygen saturation during labor where the saturation of interest is below 70%, a typical range of interest being between 15% and 65%. Attempting to match or balance the rates of absorption and scattering of the two wavelengths in a fetal sensor is particularly useful since the amount of perturbation induced artifacts is so severe in number and magnitude. For example, for a surface reflection sensor, it is difficult to know a priori where on the fetus the sensor will be located. For example, sometimes it will be on the head, other times the cheek. Hence, the tissue composition varies from application to application. In addition, the force by which the sensor is applied will vary during labor thus introducing still additional perturbation induced artifacts.
Another embodiment is to use the sensor for cardiac patients whose range of saturation, where accuracy in calculations is important, is from 50% to 80%.
In choosing an optimum LED wavelength, it should be kept in mind that LEDs have a spectral width, and are not a single narrowband wavelength device like a laser.
Sensor 200 is connected to a pulse oximeter 220. The oximeter includes a microprocessor 222 connected to an internal bus 224. Also connected to the bus is a RAM memory 226 and a display 228. A time processing unit (TPU) 230 provides timing control signals to light drive circuitry 232 which controls when light source 210 is illuminated, and if multiple light sources are used, the multiplexed timing for the different light sources. TPU 230 also controls the gating-in of signals from photodetector 214 through an amplifier 233 and a switching circuit 234. These signals are sampled at the proper time, depending upon which of multiple light sources is illuminated, if multiple light sources are used. The received signal is passed through an amplifier 236, a low pass filter 238, and an analog-to-digital converter 240. The digital data is then stored in a queued serial module (QSM) 242, for later downloading to RAM 26 as QSM 242 fills up. In one embodiment, there may be multiple parallel paths of separate amplifier filter and A/D converters for multiple light wavelengths or spectrums received.
A detector and decoder module 242 determines the wavelength of the light source from encoder 216. One embodiment of circuitry for accomplishing this is shown in commonly assigned U.S. Pat. No. 4,770,179, the disclosure of which is hereby incorporated by reference.
Based on the value of the received signals corresponding to the light received by photodetector 214, microprocessor 222 will calculate the oxygen saturation using well-known algorithms. These algorithms require coefficients, which may be empirically determined, corresponding to, for example, the wavelengths of light used. These are stored in a ROM 246. The particular set of coefficients chosen for any pair of wavelength spectrums is determined by the value indicated by encoder 216 corresponding to a particular light source in a particular sensor 200. In one embodiment, multiple resistor values may be assigned to select different sets of coefficients. In another embodiment, the same resistors are used to select from among the coefficients appropriate for an infrared source paired with either a near red source or far red source. The selection between whether the near red or far red set will be chosen can be selected with a control input from control inputs 254. Control inputs 254 may be, for instance, a switch on the pulse oximeter, a keyboard, or a port providing instructions from a remote host computer.
Both modeling and prototypes may be used to achieve the optimized sensor set forth herein. Several theoretical models exist for describing the scattering of light within tissue. The models used by the inventors assume isotropic scattering within a homogeneous tissue bed. Even though this is a simplification of the true nature of light scattering in tissue (tissue is inhomogeneous and light is scattered primarily in the forward direction), these models are useful for predicting behaviors of pulse oximetry, and the sensitivity to many design parameters.
Utilizing such a model, different choices of LED wavelengths were explored. Tissue characteristics were numerically defined and the basis (calibration) correlation between SaO2 and modulation ratio was calculated for each wavelength pair considered. Change in physiological condition was simulated by revising one or more of the numerically defined physical parameters. SpO2 was recalculated from the resulting modulation ratio, and the saturation region where errors were minimized was noted. For arterial saturations above 80% the conventional wavelength choice of 660 nm paired with 890 nm results in optimum performance, while for arterial saturations below 70%, 735 nm band emitters paired with 890 nm gives improved stability.
Sensitivity of the calibration to a change in tissue blood concentration is shown for several pairings of red and IR wavelengths. In each case, the LED has no secondary emission, and the perturbation is in going from a nominal 2% blood concentration in the tissue to 0.5%.
Figure Table IR LED red LED 805 nm 890 nm 940 nm 660 nm 7 8 9 700 nm 10 730 nm 11 12 13 760 nm 14 15 16 790 nm 17 18
When using an LED pair near 730 nm and 890 nm for pulse oximetry, the sensitivity of modulation ratio to changes in oxygen saturation (i.e., the slope of the curve in, for example,
Empirical tests on sheep were conducted using prototype sensors. The empirical observations support the use of 735 nm band red LEDs in the design of a pulse oximeter that is more robust to perturbation induced artifacts at the lower saturation region. Reflectance pulse oximetry sensors were fabricated using conventional 660-890 nm LED pairs, and with 735-890 nm pairs.
As can be seen, the diagonal line in
Using the 660 nm sensor with center-to-center emitter/detector spacing of 14 mm at the tissue,
Using the 735 nm sensor with a 5.8 mm center-to-center emitter/detector spacing at the tissue, the bias between the head and neck is greatly reduced as illustrated by
It was experimentally confirmed that increasing the emitter/detector center-to-center spacing from 5.8 mm for 735 nm/890 nm LED wavelengths decreased the sensitivity to perturbation induced artifacts, with good performance being achieved by an emitter/detector separation equal to or greater than 10 mm.
Both the modeling and the actual experiments illustrate an improvement in reliability of a saturation measurement achieved by optimizing the red wavelength to be within 700-790 nm range. In addition, reduction of the saturation error reading in the presence of force artifact is achieved by increasing the spacing of the emitters from the detector.
The force applied to the sensor causes exsanguination of the surface tissue, further magnifying the remaining disparities due to the inhomogeneity of the tissue, or causing shunting of light between the emitter and detector, thus causing errors in the saturation calculation. These are compensated for by wider emitter/detector spacing, which results in the light from the red and infrared LEDs penetrating deeper into the tissue, thus increasing the likelihood of their going through, on the average, the same combination of tissue structures, as illustrated in
The modeling and empirical tests show that the nature of the correlation between modulation ratio and saturation in pulse oximetry is related to tissue optical properties, and that the sensitivity to varying perturbation induced artifacts can be affected by choice of emitter wavelengths. For high oxygen saturations, the choice of 660 nm and 890 nm band emitters is well suited for stable pulse oximetry calculations, while 700-790 nm and 890 nm band emitters perform better at low saturations. Other wavelength combinations may be chosen from elsewhere in the visible and near infrared portion of the spectrum by following an analysis similar to the one described here. Currently, however, overall instrument design considerations (e.g., electronic signal-to-noise and potential shunting of light with narrowly spaced components in a reflectance probe) favor the use of the wavelengths discussed. By using the analysis described, other improvements to pulse oximetry are possible.
The electrical connection to emitter 114 is provided through lead 138 on one side up through the conductive epoxy, and through the other side via a wire bond 140, which connects to the other lead 134. Similarly, lead 134 connects through conductive epoxy 130 to the second emitter 112, with the other side of emitter 112 connected via a wire bond 142 to lead 138. Accordingly, as can be seen, applying a voltage with a first polarity to the two leads 134 and 138 will turn on one of the emitters, and turn off the other, while reversing the polarity will reverse which emitter is turned on and which emitter is turned off. Both of the emitters and their corresponding substrates are encapsulated in a package 144 which may, for instance, be plastic.
As an alternative to using a far red and an infrared LED, other methods for producing selected light spectrums of two different wavelengths can be used. For example, lasers could be used rather than LEDs. Alternately, a white light or other light source could be used, with the wavelength being optimized at the detector. This could be done by using appropriate filters in front of either the light source or the detector, or by using a wavelength sensitive detector. If filters are used, they could be placed in front of alternate detectors or emitters, or filters could be alternately activated in front of a single emitter or detector.
A pulse oximeter for use over a broad saturation range can utilize multiple wavelength pairs (e.g., both 660 nm and 730 nm band emitters coupled with a 900 nm emitter), with the appropriate emitter pair chosen for use in the calculation of SpO2 based on the estimated value of the oxygen saturation.
Such a pulse oximeter could be implemented with two or more red LEDs, or alternately could be implemented with a single light source and multiple filters, or multiple wavelength sensitive detectors. Different red wavelength spectrums could be utilized, based on the saturation of the patient.
As will be understood by those with skill in the art, the present invention can be embodied in other specific forms without departing from the essential characteristics thereof The wavelength could be varied while still optimizing in accordance with the present invention. Also, light pipes, light fibers, multiple filters, or multiple detectors could be used in accordance with the concepts of the present invention. Different sensors than the fulcrum structure as set forth in
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US7698909||13 Feb 2004||20 Abr 2010||Nellcor Puritan Bennett Llc||Headband with tension indicator|
|US7809420||26 Jul 2006||5 Oct 2010||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7810359||1 Oct 2003||12 Oct 2010||Nellcor Puritan Bennett Llc||Headband with tension indicator|
|US7813779||26 Jul 2006||12 Oct 2010||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7822453||28 Jul 2006||26 Oct 2010||Nellcor Puritan Bennett Llc||Forehead sensor placement|
|US7877126||26 Jul 2006||25 Ene 2011||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7877127||26 Jul 2006||25 Ene 2011||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US7899509||28 Jul 2006||1 Mar 2011||Nellcor Puritan Bennett Llc||Forehead sensor placement|
|US7979102||21 Feb 2006||12 Jul 2011||Nellcor Puritan Bennett Llc||Hat-based oximeter sensor|
|US8219170||20 Sep 2006||10 Jul 2012||Nellcor Puritan Bennett Llc||System and method for practicing spectrophotometry using light emitting nanostructure devices|
|US8257274||25 Sep 2008||4 Sep 2012||Nellcor Puritan Bennett Llc||Medical sensor and technique for using the same|
|US8265724||9 Mar 2007||11 Sep 2012||Nellcor Puritan Bennett Llc||Cancellation of light shunting|
|US8364220||25 Sep 2008||29 Ene 2013||Covidien Lp||Medical sensor and technique for using the same|
|US8396524||27 Sep 2006||12 Mar 2013||Covidien Lp||Medical sensor and technique for using the same|
|US8412297||28 Jul 2006||2 Abr 2013||Covidien Lp||Forehead sensor placement|
|US8423112||30 Sep 2008||16 Abr 2013||Covidien Lp||Medical sensor and technique for using the same|
|US8452367||26 Jul 2010||28 May 2013||Covidien Lp||Forehead sensor placement|
|US8515515||11 Mar 2010||20 Ago 2013||Covidien Lp||Medical sensor with compressible light barrier and technique for using the same|
|US8521247||29 Dic 2010||27 Ago 2013||Covidien Lp||Certification apparatus and method for a medical device computer|
|US8781548||11 Mar 2010||15 Jul 2014||Covidien Lp||Medical sensor with flexible components and technique for using the same|
|US8818473||30 Nov 2010||26 Ago 2014||Covidien Lp||Organic light emitting diodes and photodetectors|
|US8923944||20 Ago 2012||30 Dic 2014||Covidien Lp||Cancellation of light shunting|
|Clasificación de EE.UU.||600/338, 600/323, 600/344|
|Clasificación cooperativa||A61B5/1464, A61B5/14542, A61B5/7207, A61B2562/0242|
|Clasificación europea||A61B5/1464, A61B5/145N|