MEDICAL SENSOR WITH COMPRESSIBLE LIGHT BARRIER AND TECHNIQUE FOR USING THE SAME

[0001] This claims the benefit of U.S. Provisional patent Application No. 61/163,358, filed Mar. 25, 2009, which is hereby incorporated by reference herein in its entirety.

[0002] The present disclosure relates generally to medical devices and, more particularly, to sensors used for sensing physiological parameters of a patient.

[0003] This section is intended to introduce the reader to aspects of the art that may be related to various aspects of the present disclosure, which are described and/or 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 disclosure. Accordingly, it should be understood that these statements are to be read in this light, and not as admissions of prior art.

[0004] In the field of medicine, doctors often desire to monitor certain physiological characteristics of their patients. Accordingly, a wide variety of devices have been developed for monitoring many such physiological characteristics. Such devices provide doctors and other healthcare 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.

[0005] One technique for monitoring 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 oximeters. Pulse oximetry may be used to measure various blood flow characteristics, such as the blood-oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the tissue, and/or the rate of blood pulsations corresponding to each heartbeat of 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.

[0006] Pulse oximeters typically utilize a non-invasive sensor that transmits light through a patient's tissue and that photoelectrically detects the absorption and/or scattering of the transmitted light in such tissue. One or more of the above physiological characteristics may then be calculated based upon the amount of light absorbed and/or scattered. More specifically, the light passed through the tissue is typically selected to be of one or more wavelengths that may be absorbed and/or scattered by the blood in an amount correlative to the amount of the blood constituent present in the blood. The amount of light absorbed and/or scattered may then be used to estimate the amount of blood constituent in the tissue using various algorithms.

[0007] Pulse oximetry readings involve placement of a sensor on a patient's tissue, typically via a lightly adhesive sensor, a clip-style sensor, or a sensor that may be fitted into a wearable garment, such as a hat or a headband. If the hat or headband is not closely fitted to the patient's tissue, ambient light may interfere with the sensor's light detection. Some outside light infiltration into the sensor may be avoided by fitting the sensor snugly against the patient's tissue. However, such a conforming fit may be difficult to achieve over a range of patient physiologies without adjustment or excessive attention on the part of medical personnel. Additionally, an overly tight fit may cause local exsanguination of the tissue around the sensor. Exsanguinated tissue, which is devoid of blood, may shunt the sensor light through the tissue, which may also result in increased measurement errors.

[0019] One or more specific embodiments of the present disclosure will be described below. In an effort to provide a concise description of these embodiments, not all features of an actual implementation are described in the specification. It should be appreciated that in the development of any such actual implementation, as in any engineering or design project, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, 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.

[0020] Optical medical sensors are provided that reduce the amount of outside light that may impinge the detecting elements of a sensor. Such sensors may also reduce the amount of “shunted” light, i.e., light originating from light emitting elements of the sensor that impinges the detecting elements of a sensor without first passing through tissue. Such sensors may incorporate surface features on the tissue-contacting surface of the sensor to influence the path of light from the undesired light sources and/or to direct such light away from the detecting elements of the sensor. Such sensors may absorb or reflect the light originating from these undesired light sources before such light can impinge the detecting elements of the sensor.

[0021] Pulse oximetry sensors are typically placed on a patient in a location that is normally perfused with arterial blood to facilitate measurement of the desired blood characteristics, such as arterial oxygen saturation measurement (SpO₂). The most common sensor sites include a patient's fingertips, toes, earlobes, or forehead. Regardless of the placement of a sensor used for pulse oximetry, the reliability of the pulse oximetry measurement is related to the accurate detection of transmitted light that has passed through the perfused tissue and that has not been supplemented by undesired light sources. Such supplementation and/or modulation of the signals transmitted to a monitor by the sensor can cause variability in the resulting pulse oximetry measurements. The contribution of ambient and/or shunted light may affect the measurement of the particular blood constituent, such as SpO₂.

[0022] In many cases, light from undesired light sources propagates along an optical path that is distinguishable from the optical path of the light that is related to a blood constituent. In a transmission-type sensor, the sensor's emitter and detector lie on opposing sides of the tissue when the sensor is applied to a patient. The optical path of the signal light, which is light originating from the emitter that properly passes through perfused tissue, is substantially in-line with an imaginary axis connecting the emitter and the detector. For reflectance-type sensors, the optical path of the emitted signal light is somewhat more complicated, as the light first enters the perfused tissue and then is scattered back to the detector. In both transmission-type and reflectance-type sensors, shunted light and ambient light generally propagate at angles substantially off-axis from the optical path of the signal light.

[0023] The sensors discussed below have compressible light barriers that act to divert shunted and/or ambient light away from the light detecting elements of a sensor. In an embodiment, an oximetry sensor with such compressible light barriers may be adapted for placement in a hat (for example, a neonatal stocking cap), a headband, or other wearable structure (i.e. a glove, a sock, a wristband) to apply the sensor on the body of the user. FIGS. 1A-1D illustrate an assembly drawing of an embodiment of a sensor assembly 10 including a wearable structure, which may be a hat 11, as shown in FIG. 1A. A reflectance-type pulse oximetry sensor 15, as shown in FIG. 1B, is adapted to be placed or adhered to the inside of the hat 11. The sensor 15 may include a substrate 14 that may be made from any suitable material. In an embodiment, the substrate 14 is a foam or other conformable material. In one embodiment, the substrate 14 is black or dark in color to absorb stray light and further minimize any shunting of light between sensor and patient skin. The substrate 14 may include an adhesive material to secure the sensor directly to the tissue. In one embodiment, the sensor 15 may include an emitter 16 containing emitters for two or more wavelengths of lights and a detector 18 spaced apart from the emitter 16. The sensor 15 also may include compressible light barrier 12, discussed in more detail below, configured to block undesired light from reaching the detector 18.

[0024] Also shown in FIG. 1B is a cable 20 for providing drive current to the LED component of the emitter 16, and providing the detector signal to the medical device. In addition to providing the electrical connection to the downstream medical device, the cable 20 may provide shielding to protect the signals from the detector against external electrical interference. In addition, the sensor 15 may include suitable structures for providing electrical connections to the cable 20 and/or downstream medical device, such as a flex circuit, a Faraday shield, and leads connecting the optical components of the sensor 15 to the electrical components.

[0025] FIG. 1C is a cross-sectional side view showing the compressible light barrier 12 that substantially surrounds emitter 16. The compressible light barrier 12 may protrude from the surface 14 of the sensor 15. When the hat 11 is applied to the tissue, the force of the elastic band or knit of the hat 11 may provide sufficient force such that the compressible light barrier 12 is compressed against the tissue to form a seal. Any light from the emitter 16 on a path, represented by arrow 23, to shunt directly to the detector 18 is blocked by the interior walls 22 of the compressible light barrier 12. Accordingly, light from the emitter 16 may be directed towards the tissue and away from the shunt path to the detector 18, which may improve the accuracy of measurements from the sensor 15.

[0026] As shown, the compressible light barrier 12 surrounds the emitter 16. However, in embodiments the compressible light barrier 12 may surround the detector 18, or both the emitter 16 and the detector 18, or may be disposed in a region between the emitter 16 and the detector 18. In an embodiment, it may be advantageous for the footprint of the compressible light barrier 12 on the surface 14 to be minimized. For example, while the compressible light barrier 12 may act to prevent unwanted light from reaching the detector, the compressible light barrier 12, because it protrudes from the surface 14, may also interfere with a conforming fit of the sensor 15 to the tissue. Accordingly, a balance between the light barrier properties and the conforming fit may be achieved by providing the compressible light barrier 12 on less than 25%, less than 20%, less than 15%, less than 10%, or less than 5% of the surface 14. This may be achieved by providing the compressible light barrier 12 with relatively thin walls, or by surrounding only one of the emitter 16 and the detector 18 rather than both. In an embodiment, the compressible light barrier 12 surrounding the emitter 16 may have a different, or smaller, shape than the compressible light barrier 12 surrounding the detector 18. For example, it may be advantageous to have a smaller compressible light barrier 12 surrounding the emitter 16 to more narrowly focus the light directed towards the tissue. In addition, the compressible light barrier 12 may be configured to protrude minimally from the surface 14. The compressible light barrier 12 may protrude from the surface 14 at least about 0.5 mm, 1 mm, 2 mm, or 5 mm in its uncompressed state. It should be understood that the compressible light barrier 12, when compressed by the force of application of the sensor 15 to the tissue, may protrude only slightly from the surface 14. For example, the compressible light barrier 12 may protrude from the surface 14 about 0.5 mm, 1 mm, 2 mm, in its uncompressed state. A compressible light barrier 12 that is 5 mm in height in its uncompressed state may be compressed to a height of 2.5 mm (50% of its uncompressed height) or 1.25 mm (25% of its uncompressed height). Similarly, a compressible light barrier 12 that is 2 mm in height in its uncompressed state may be compressed to a height of 1 mm (50% of its uncompressed height) or 0.5 mm (25% of its uncompressed height).

[0027] In an embodiment, the compressible light barrier 12 is formed from materials with low durometer or a high degree of compressibility, such as foams, silicone, polyvinyl chloride, or gels, for example, a material having a compression modulus of about 2.0 or less. The compression modulus for polyurethane foam is a function of the density of the foam and the structure of the foam. Generally, compression modulus increases as foam density increases. In embodiments, different chemical formulations and manufacturing processes may be used to create foams with different foam cell structures. Foams with high concentration of closed cells (closed-cell foam) typically have a higher compression modulus than foams with high concentration of open cells (open-cell foam). In an embodiment, compressibility may be measured by an Indention Load Deflection (ILD) test, which measures the load-bearing capacity of a standard specimen indented by a circular compressor foot of 50 square inches as 25% deflection. The sample is placed on a perforated plate (perforated plate has ¼″ holes on ¾″ centers) and is deflected twice to 25% of its original height and then allowed to relax for 10+/− minutes. The height of the foam is then rechecked. The new height is determined and then the sample is deflected 25%, or to 75% of the crushed height. The foam is then held in this fashion for one minute and the load on the scale is then read. In one embodiment, the ratio (compression modules) of the compressive force needed to indent the foam to 25% and 50%, respectively, of its thickness is determined. The greater the value of this ratio, the greater the degree of firmness that is offered by the foam. Low density foams have a compression modulus of around 1.20. In embodiments, the compression modulus of the compressible light barrier 12 may be less than about 2.0, less than about 1.5 or less than about 1.2.

[0028] The sensor assembly 10 is shown fully assembled in FIG. 1D. As shown, the sensor 15 is positioned on the interior of the hat 11 such that the emitter 16 and detector 18 may come into contact with the skin when the sensor assembly 10 is applied to a patient. The sensor 15 may be attached (e.g., adhered or sewn into) to the inside band of the hat 11. In one embodiment, the hat 11 may include indicators to position the sensor 15 on a particular location on the patient's forehead, for example to position the sensor 15 on the lower forehead region, above the eyebrow, with the sensor optics (emitter 16 and detector 18) located above and predominantly lateral to or centered over the iris. The location of the reflectance sensor 15 in the hat allows appropriate placement of the sensor in the desired forehead location by a user. FIG. 1D shows that the cable 20 is positioned through a hole in the top of the hat 11. In an embodiment, the cable 20 may be adhered or otherwise constrained in the hat 11 so that the cable 20 generally is positioned away from the sensor 15 to avoid interfering with the patient's eyesight or bothering the patient.

[0029] In an embodiment, the force of the sensor 15 against the tissue, including any force provided by the compressible light barrier 12, may not exsanguinate the tissue. In one embodiment, it is contemplated that the force that hat 11 (or other wearable assembly, such as a headband or clip-style sensor) exerts on the tissue sufficient pressure so that the pressure exceeds the typical venous pressure of a patient, but does not exceed the diastolic arterial pressure. As the pulse oximetry measurements are related to arterial blood oxygen saturation and pulsation, and not venous blood pulsation, reducing the effect of the venous component in the tissue may enhance the sensitivity of the sensor to variations in the arterial blood signal. Thus, the sensor assembly 10 may apply a pressure greater than the venous pressure to squeeze excess pooled venous blood from the optically probed tissue. Yet, since the pressure applied by the sensor assembly 10 is designed to be less than the arterial pressure, the application of pressure to the tissue does not interfere with the arterial pulse signal. Typical venous pressure, diastolic arterial pressure, and systolic arterial pressure are less than 10-35 mmHg, 80 mmHg, and 120 mmHg, respectively. Accordingly, in certain embodiments, the sensor assembly 10 may be adjusted to overcome an average venous pressure of 15-35 mmHg. However, venous pressures may vary because of the location of the vascular bed and the patient's condition. For example, low arterial diastolic blood pressure (about 30 mmHg) may occur in sick patients. In such embodiments, the sensor assembly 10 removes most of the venous pooling with by applying sufficient pressure to overcome light to moderate venous pressure (about 15 mmHg).

[0030] In one embodiment, the force applied to the tissue to overcome the venous pressure may be sufficient to compress the compressible light barrier 12 to an appropriate degree, for example to at least 50% of its original uncompressed height or at least 25% of its original uncompressed height, so that the light barrier properties remain intact. In another embodiment, if the force applied to the sensor is increased, the compressible light barrier 12 may act as a pressure absorber, preventing the skin from becoming exsanguinated in the case of an inappropriately high pressure. In such an embodiment, the compressible light barrier 12 may then be compressed to an even greater degree, so that it lies substantially flush with the surface 14.

[0031] It should be appreciated that the compressible light barrier 12 may be arranged in any suitable manner on the surface of the sensor 15 to prevent ambient or shunted light from reaching the detector 18. In an embodiment, shown in FIG. 2 and FIG. 3, compressible light barrier 12 may be arranged to surround the emitter 16 and the detector 18. FIG. 2 is a perspective view of an exemplary forehead sensor 24 with a compressible light barrier 12 that includes concentric circles 26 that substantially surround an emitter 16 and a detector 18, and FIG. 3 is a cross-sectional view of the sensor 24 applied to a patient's forehead 28. Such an arrangement of concentric circles 26 may be advantageous in forming a seal with the tissue 28, thus creating a barrier against any ambient light or shunted light that may leak into the sensor 24. The ambient light, depicted by wavy arrows 30, impinges the compressible light barrier 12 and is prevented from reaching the detector 18. The optical path of the signal light, depicted by wavy arrow 32, is substantially unaffected by the compressible light barrier 12.

[0032] In one embodiment, the compressible light barrier 12 may include light absorbing materials, light reflecting materials, light refracting materials, or any combination thereof. For example, a surface, including all or part of a compressible light barrier 12, may be formed from, coated with, or impregnated with such materials. It should also be appreciated that, as discussed above, the compressible light barrier 12 may contain such materials only on a tissue-contacting surface, or, in alternate embodiments, the sensor body may be constructed entirely from such materials in appropriate regions as described herein. As shown in FIG. 4, a cross-sectional view of a sensor 32, the compressible light barrier 12 surrounding the emitter 16 may include a light reflective surface 34 and a light absorptive surface 36. As shown, the light surface 34 may face the emitter 16, while the light absorptive surface 36 may be surfaces that do not face the emitter 16. Such an arrangement may allow off-angle light from the emitter 16 to be reflected back towards the tissue, which may help to increase the signal intensity received at the detector 18. In addition, dark or absorptive surfaces on other areas of the compressible light barrier 12 may absorb ambient light that leaks from the edges of the sensor 32. Similarly, the compressible light barrier 12 surrounding the detector 18 may include a light reflective surface 34 to help redirect light towards the detector 18 while absorptive surface 36 may absorb shunted or ambient light before it reaches the detector 18. Examples of light absorbing materials may include, but are not limited to, black or dark pigment, black or dark woven fabric or cloth, and infrared blockers. Examples of suitable light reflecting materials include white or silver pigment, metals, or mirrored surfaces. Further, the surface 40 of the sensor 32 may be light reflective or light absorptive.

[0033] It should also be appreciated that light absorbing materials may be adapted to absorb light at a particular wavelength. In certain embodiments, when light absorbing material is disposed between an emitter and a detector of a sensor, it may be advantageous to use light absorbing material that absorbs a wavelength emitted by the emitter in order to absorb shunted light from the emitter. For example, a light absorbing material may absorb at least about 50% of one or more wavelengths of light from the emitter, or may absorb a range of 50% to 95% of one or more wavelengths of light from the emitter. A light absorbing material may also absorb at least about 90% to at least 95% of one or more wavelengths of visible light and near-infrared light. In a specific embodiment, a pulse oximetry sensor may emit at least one wavelength of light in the wavelength range of 500 nm-1000 nm. For example, a sensor may emit light and wavelengths of 660 nm and 900 nm, which are wavelengths that may be absorbed by dark pigment.

[0034] FIG. 5 illustrates an embodiment of a headband-based sensor assembly 50 that includes a medical sensor 44 and with a compressible light barrier 12. The headband-based sensor assembly 50 may include a strap or band 52 that may be fitted around a patient's forehead tissue to contact the sensor 34 with the tissue. In certain embodiments, the sensor 44 may send feedback to a downstream monitor through cable 20 relating to one or more blood or tissue constituents.

[0035] A sensor or sensor assembly, illustrated generically as a sensor assembly 10, may be used in conjunction with a pulse oximetry monitor 60, as illustrated in FIG. 6. It should be appreciated that the cable 20 of the sensor assembly 10 may be coupled to the monitor 60 or it may be coupled to a transmission device to facilitate wireless transmission between the sensor assembly 10 and the monitor 60. The monitor 60 may be any suitable pulse oximeter, such as those available from Nellcor Puritan Bennett LLC. Furthermore, to upgrade conventional pulse oximetry provided by the monitor 60 to provide additional functions, the monitor 60 may be coupled to a multi-parameter patient monitor 62 via a cable 64 connected to a sensor input port or via a cable 66 connected to a digital communication port.

[0036] FIG. 7 is a block diagram of an embodiment of a pulse oximeter 60 that may be configured to implement the embodiments of the present disclosure. Light from emitter 16 may pass into a blood perfused tissue, and may be scattered, and then detected by detector 18. A sensor assembly 10 containing an emitter 16 and a detector 18 may also contain an encoder 70 which may be capable of providing signals indicative of the wavelength(s) of light source 16 to allow the oximeter to select appropriate calibration coefficients for calculating oxygen saturation. The encoder 70 may, in an embodiment, be a resistor.

[0037] In an embodiment, the sensor assembly 10 may be connected to a pulse oximetry monitor 60. The monitor 60 may include a microprocessor 72 coupled to an internal bus 74. Also connected to the bus may be a RAM memory 76 and a display 78. A time processing unit (TPU) 80 may provide timing control signals to light drive circuitry 82, which controls when the emitter 16 is activated, and if multiple light sources are used, the multiplexed timing for the different light sources. TPU 80 may also control the gating-in of signals from detector 18 through an amplifier 83 and a switching circuit 84. These signals are sampled at the proper time, depending at least in part upon which of multiple light sources is activated, if multiple light sources are used. The received signal from the detector 18 may be passed through an amplifier 86, a low pass filter 88, and an analog-to-digital converter 90. The digital data may then be stored in a queued serial module (QSM) 92, for later downloading to RAM 76 or ROM 96 as QSM 92 fills up.

[0038] In an embodiment, based at least in part upon the received signals corresponding to the light received by detector 18, microprocessor 72 may calculate the oxygen saturation using various algorithms. These algorithms may require coefficients, which may be empirically determined, and may correspond to the wavelengths of light used. The algorithms may be stored in a ROM 96 and accessed and operated according to microprocessor 72 instructions. For example, the encoder 70 may communicate with decoder 71 to allow the microprocessor 72 to determine the appropriate coefficients.

[0039] In an embodiment of a two-wavelength system, the particular set of coefficients chosen for any pair of wavelength spectra may be determined by a value indicated by the encoder 70 corresponding to a particular light source in a particular sensor assembly 10. In one embodiment, multiple resistor values may be assigned to select different sets of coefficients, or the sets of coefficients may be stored on a digital medium. In another embodiment, the 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 94. Control inputs 94 may be, for instance, a switch on the pulse oximeter, a keyboard, or a port providing instructions from a remote host computer. Furthermore, any number of methods or algorithms may be used to determine a patient's pulse rate, oxygen saturation or any other desired physiological parameter.

[0040] The sensor assembly 10 includes an emitter 16 and a detector 18 that may be of any suitable type. For example, the emitter 16 may be one or more light emitting diodes adapted to transmit one or more wavelengths of light in the red to infrared range, and the detector 18 may one or more photodetectors selected to receive light in the range or ranges emitted from the emitter 16. Alternatively, an emitter 16 may also be a laser diode or a vertical cavity surface emitting laser (VCSEL). An emitter 16 and detector 18 may also include optical fiber sensing elements. An emitter 16 may include a broadband or “white light” source, in which case the detector could include any of a variety of elements for selecting specific wavelengths, such as reflective or refractive elements or interferometers. These kinds of emitters and/or detectors would typically be coupled to the rigid or rigidified sensor via fiber optics. Alternatively, a sensor assembly 10 may sense light detected from the tissue is at a different wavelength from the light emitted into the tissue. Such sensors may be adapted to sense fluorescence, phosphorescence, Raman scattering, Rayleigh scattering and multi-photon events or photoacoustic effects.

[0041] For pulse oximetry applications using either transmission or reflectance type sensors the oxygen saturation of the patient's arterial blood may be determined using two or more wavelengths of light, most commonly red and near infrared wavelengths. Similarly, in other applications, a tissue water fraction (or other body fluid related metric) or a concentration of one or more biochemical components in an aqueous environment may be measured using two or more wavelengths of light, most commonly near infrared wavelengths between about 1,000 nm to about 2,500 nm. It should be understood that, as used herein, the term “light” may refer to one or more of ultrasound, radio, microwave, millimeter wave, infrared, visible, ultraviolet, gamma ray or X-ray electromagnetic radiation, and may also include any wavelength within the radio, microwave, infrared, visible, ultraviolet, or X-ray spectra.

[0042] The emitter 16 and the detector 18, and the compressible light barrier 12, may be disposed on a sensor body, which may be made of any suitable material, such as plastic, foam, woven material, or paper. Alternatively, the emitter 16 and the detector 18 may be remotely located and optically coupled to the sensor assembly 10 using optical fibers. In the depicted embodiments, the sensor assembly 10 is coupled to a cable that is responsible for transmitting electrical and/or optical signals to and from the emitter 16 and detector 18 of the sensor assembly 10. The cable may be permanently coupled to the sensor assembly 10, or it may be removably coupled to the sensor assembly 10—the latter alternative being more useful and cost efficient in situations where the sensor assembly 10 is disposable.

[0043] The sensor assembly 10 may be a “transmission type” sensor. Transmission type sensors include an emitter 16 and detector 18 that are typically placed on opposing sides of the sensor site. If the sensor site is a fingertip, for example, the sensor assembly 10 is positioned over the patient's fingertip such that the emitter 16 and detector 18 lie on either side of the patient's nail bed. In other words, the sensor assembly 10 is positioned so that the emitter 16 is located on the patient's fingernail and the detector 18 is located 180° opposite the emitter 16 on the patient's finger pad. During operation, the emitter 16 shines one or more wavelengths of light through the patient's fingertip and the light received by the detector 18 is processed to determine various physiological characteristics of the patient. In each of the embodiments discussed herein, it should be understood that the locations of the emitter 16 and the detector 18 may be exchanged. For example, the detector 18 may be located at the top of the finger and the emitter 16 may be located underneath the finger. In either arrangement, the sensor assembly 10 will perform in substantially the same manner.

[0044] Reflectance type sensors also operate by emitting light into the tissue and detecting the light that is transmitted and scattered by the tissue. However, reflectance type sensors include an emitter 16 and detector 18 that are typically placed on the same side of the sensor site. For example, a reflectance type sensor may be placed on a patient's fingertip or forehead such that the emitter 16 and detector 18 lie side-by-side. Reflectance type sensors detect light photons that are scattered back to the detector 18. A sensor assembly 10 may also be a “transflectance” sensor, such as a sensor that may subtend a portion of a baby's heel.

[0045] While the disclosure may be susceptible to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and have been described in detail herein. However, it should be understood that the embodiments provided herein are not intended to be limited to the particular forms disclosed. Indeed, the disclosed embodiments may not only be applied to measurements of blood oxygen saturation, but these techniques may also be utilized for the measurement and/or analysis of other blood constituents. For example, using the same, different, or additional wavelengths, the present techniques may be utilized for the measurement and/or analysis of carboxyhemoglobin, met-hemoglobin, total hemoglobin, fractional hemoglobin, intravascular dyes, and/or water content. Rather, the various embodiments may cover all modifications, equivalents, and alternatives falling within the spirit and scope of the disclosure as defined by the following appended claims