Patent Description:
Pulse oximeters are a common device used in clinical settings. Pulse oximeters are used for monitoring a blood-oxygen saturation (SpO<NUM>) level of patients. Typically, in clinical environment settings, a pulse oximeter can be attached (i.e., hooked on) to a patent, and the pulse oximeter continuously measures the SpO<NUM> level. Since the pulse oximeter needs to be continuously attached to the patient, the pulse oximeter is designed so that it is not attached too tightly to the patient's body part. This device is typically hooked on to one of the index fingers (or any other finger) in adult patients. For pediatric uses, the device is designed to be hooked to leg of the patient. The pulse oximeter should be loose enough so that it does not hurt or cause discomfort to the patient due to long duration of usage. However, this kind of design makes the device vulnerable to movements when patient body moves.

The pulse oximeter is configured to determine SpO<NUM> level based on a measured difference in the absorption of red and infrared light by hemoglobin (Hb) and oxygenated hemoglobin (HbO<NUM>), and also based on volume of arterial blood in the measuring area of the tissue. Any change or disturbance to the measured difference in the absorption, or in the measured volume, affect the final SpO<NUM> reading from the pulse oximeter. For example, motion by a patient may induce a change in the location of measurement of the SpO<NUM> area. This change can lead to differences in the SpO<NUM> reading since not every area of body tissue has the same volume of arterial blood. Another factor that governs measurement accuracy of SpO<NUM> is a light source of the device, as this can impact accuracy of the measured difference in absorption in the red and infrared (IR) wavelengths or ranges. However, pulse oximeters are typically applied externally (e.g. using a clip that attaches to a finger, earlobe, infant's foot, or so forth), and in these arrangements a gap commonly exists between the light detector sensor and patient skin. This gap can allow ambient light to fall on the light detector of the device, and contribute noise which can adversely impact accuracy of the SpO<NUM> measurement.

<CIT> discloses a health monitoring apparatus. In an example, an optical transducer comprises a light source and a photo-detector. The light source generates red and infrared radiation, which is detected by the photo-detector.

<CIT> discloses a blood pressure sensor. In an example, a PPG sensor unit has an array of photodetectors and an LED. To resolve ambient light problems, ambient light is separated on the basis of the differential response among detectors of the array.

The following discloses new and improved systems and methods to overcome these problems.

In one disclosed aspect, an oxygen saturation monitor includes a clamp having opposing first and second clamp portions. An array of light sources is disposed on the first clamp portion. Each light source is switchable between (i) off, (ii) emitting light of a first wavelength or spectral range, (iii) emitting light of a second wavelength or spectral range different from the first wavelength or spectral range; and (iv) emitting light at both the first and second wavelengths or spectral ranges. An array of light detectors is disposed on the second clamp portion facing the array of light sources. Each light detector of the array of light detectors is aligned to detect emitted light from a corresponding light source of the array of light sources.

One advantage resides in providing measurement of blood oxygen saturation levels of a patient with improved accuracy.

Another advantage resides in reducing the impact of patient motion on blood-oxygen saturation level measurements.

Another advantage resides in reducing the impact of ambient light on blood-oxygen saturation level measurements.

Another advantage resides in compensating for motion-induced artifacts on blood-oxygen saturation level measurements.

Another advantage resides in providing a pulse oximeter that is less sensitive to patient movements and changes in ambient lighting.

The disclosure may take form in various components and arrangements of components, and in various steps and arrangements of steps. The drawings are only for purposes of illustrating the preferred embodiments and are not to be construed as limiting the disclosure.

A conventional clip-on style pulse oximeter has a clamp design with red and infrared light sources in one clamp piece and a light detector in the opposing clamp piece. The device is clamped onto a fingertip, ear lobe, a foot in the case of an infant, or some other body part which is thin enough for light from the light sources to transmit through the body tissue so as to be detected at the light detector. Based on a ratio of the transmitted infrared (e.g. <NUM>) versus red (e.g. <NUM>) light, the peripheral SpO<NUM> level is measured. However, the SpO<NUM> measurement can be adversely affected by stray light picked up by the light detector.

In some embodiments disclosed herein, to improve robustness against stray light, an array of IR/R light source/photodetector pairs is employed in which each IR/R light source (itself actually a pair of light sources, one emitting red light and the other IR light) is arranged to illuminate a single one of the light detectors. The illustrative array is 3x3 though other sizes are contemplated. During an SpO<NUM> measurement, only a single IR/R light source/photodetector pair is used to measure the (uncorrected) SpO<NUM> signal. Detectors neighboring the pair used to measure the SpO<NUM> signal are used to detect any stray light. The following discloses a formula for a correction factor κ for correcting the measured SpO<NUM> signal based on the intensities measured by the neighboring detectors.

In other embodiments disclosed herein, the pulse oximeter may be provided with a displacement measurement unit comprising an accelerometer and a gyroscope mounted on the device. Both translational and rotational motion can be detected with this combination. The displacement measurement can be used in various ways, such as triggering a measurement pause when the device is in motion, triggering a new computation of the stray light correction factor κ (since with the device moved it may receive different exposure to stray light), or to update the choice of IR/R light source/photodetector pair used to measure the (uncorrected) SpO<NUM> signal.

In an alternative embodiment, machine learning (ML) could be used to train the stray light correction factor κ, the displacement corrections, or both.

With reference to <FIG>, an illustrative embodiment of an oxygen saturation monitor <NUM> is shown. In some embodiments, the oxygen saturation monitor <NUM> may be a pulse oximeter, in which one or more vital signs are derived from measurements obtained from the oxygen saturation monitor. The oxygen saturation monitor <NUM> can be configured as a clamp <NUM> having a first clamp portion <NUM> and an opposing second clamp portion <NUM> coupled together by a clamping mechanism <NUM> such as a hinge with a biasing spring. In operation, the clamping mechanism <NUM> biases opposing faces 14F, 16F of the respective first and second clamp pieces <NUM>, <NUM> toward each other when the clamp <NUM> is attached to a body part. The clamping mechanism <NUM> is operative to bring the two opposing faces 14F, 16F into sufficiently close proximity to each other to ensure the body part (e.g. finger F) is securely held by the opposing faces 14F, 16F. It will be appreciated that the faces may optionally be contoured based on the expected geometry of the body part, and the clamping mechanism <NUM> is designed to provide sufficient clamping force for holding the monitor <NUM> to the body part without causing discomfort to the patient by excessive clamp pressure. As shown in <FIG>, the clamp <NUM> is configured as a finger clamp attachable to a finger F of the patient (although the clamp may be attached to any suitable portion of a patient, such as an ankle, wrist, and so forth that is thin enough for light from light sources <NUM> to transmit through the body tissue of the patient (e.g., through the finger F) so as to be detected by light detectors <NUM>). In the illustrative example, the first clamp portion <NUM> is disposed on a "top" portion of the finger and the second clamp portion <NUM> is disposed on a "bottom" portion of the finger.

It may be noted that the light sources <NUM> and the light detectors <NUM> are typically embedded in the respective faces 14F, 16F of the respective clamp portions <NUM>, <NUM> and hence may be occluded from view when the monitor <NUM> is clamped to the finger F; this is indicated in <FIG> by showing the light sources <NUM> and the light detectors <NUM> using dashed lines. It will also be noted that there may be some gap or space between the light sources <NUM> and/or the light detectors <NUM> and the finger F, as shown in <FIG>. It will be appreciated that these gaps or spaces may provide ingress paths via which stray light can reach the detectors <NUM>. Additionally, even if no such gaps are present, the body part (e.g. finger F) onto which the monitor <NUM> is clamped must be optically translucent in the red and infrared in order for light from the light sources <NUM> to reach the light detectors <NUM>, and so stray light can pass through the translucent body part to reach the light detectors <NUM>.

With continuing reference to <FIG>, and now with reference to <FIG>, the light sources <NUM> comprise an array of light sources <NUM> that is disposed on the first clamp portion <NUM>, and an array of light detectors <NUM> is disposed on the second clamp portion <NUM> facing the array of light sources as seen in <FIG>. Each light detector of the array of light detectors <NUM> is aligned to detect emitted light from a corresponding light source of the array of light sources <NUM>. As shown in <FIG>, the illustrative array of light sources <NUM> includes <NUM> light sources <NUM>-<NUM>, and the illustrative array of light detectors <NUM> includes <NUM> corresponding light detectors <NUM>-<NUM>. The light detectors <NUM>-<NUM> are arranged to only detect red and/or IR light from a corresponding light source <NUM>-<NUM> (e.g., the light detector <NUM> only detects light emitted from the light source <NUM>, the light detector <NUM> only detects light emitted from the light source <NUM>, and so forth). As shown in <FIG>, the array of light sources <NUM> and the array of light detectors <NUM> are both arranged in a 3X3 matrix, although any suitable configuration is possible. In addition, the number of light sources in the array of light sources <NUM> (and likewise the number of light detectors in the array of light detectors <NUM>) can be any suitable number other than <NUM>, so long as the number of light sources is the same as the number of light detectors).

Each of the light sources <NUM>-<NUM> of the array of light sources <NUM> is switchable between multiple modes of operation, including (i) off, (ii) emitting light of a first wavelength or spectral range, (iii) emitting light of a second wavelength or spectral range different from the first wavelength or spectral range; and (iv) emitting light at both the first and second wavelengths or spectral ranges. For example, in one embodiment the first wavelength or spectral range is red light, and the second wavelength of spectral range is infrared (IR) light. To this end, in one suitable configuration each light source <NUM>-<NUM> includes a red light source and an infrared light source. This is diagrammatically shown in <FIG>, with the constituent light sources labeled as the IR light source 18IR and the red light source 18R. (This labeling is done only for the light source <NUM> for illustrative convenience, but each of the light sources <NUM>-<NUM> similarly includes two constituent light sources).

To control operation of the light sources <NUM>-<NUM> between these multiple modes of operation, the oxygen saturation monitoring further includes at least one electronic processor <NUM> (e.g., a microprocessor) programmed to control the array of light sources <NUM> to emit switched red and infrared light by a single active light source (e.g., the light source <NUM>) of the array of light sources with all other light sources (e.g., the light sources <NUM>-<NUM> and <NUM>-<NUM>) of the array of light sources being off. This is suitably done by: activating the infrared light source 18IR to output infrared light; activating the red light source 18R to output red light; or not activating either light source 18IR or 18R when off. The electronic processor <NUM> is also programmed to control operation of the array of light detectors <NUM>. For example, the electronic processor <NUM> is programmed to control (or selectively read) the array of light detectors <NUM> to detect the switched red and infrared light using the light detector <NUM>-<NUM> aligned to detect emitted light from the single active light source emitted from a corresponding central light source (e.g., the central light source <NUM> is configured to emit the light, and the corresponding light detector <NUM> is controlled to be the only light detector to detect the emitted light from the central light source). Moreover, the other light detectors (e.g., the light detectors <NUM>-<NUM> and <NUM>-<NUM>, or some subset of these other light detectors) are controlled by (or read by) the electronic processor <NUM> to detect ambient light (e.g., light not emitted from a corresponding light source <NUM>-<NUM> and <NUM>-<NUM>).

The oxygen saturation monitor <NUM> is configured to determine an oxygen saturation value of the patient (and, optionally, one or more vital signs such as a heart rate determined from the pulsatile variation of the red and/or infrared light). In some embodiments, the electronic processor <NUM> is programmed to compute a red/infrared light intensity ratio for the detected switched red and infrared light, correct the red/infrared light intensity ratio based on the detected ambient light, and convert the corrected red/infrared light intensity ratio to an oxygen saturation value.

Based on a ratio of the transmitted red R (e.g. λ<NUM>=<NUM>) light versus infrared IR (e.g. λ<NUM>=<NUM>) light, a peripheral oxygen saturation (SpO<NUM>) level is measured. For example, the ratio: <MAT> can be computed, where Iac<NUM>, Iac<NUM> are the ac components of the intensity for the red light (i.e., index ac<NUM>) and the IR light (i.e., index ac<NUM>) respectively. The signal R is converted to an SpO<NUM> reading in units of a percentage (where SpO<NUM>=<NUM>% is fully oxygenated blood) using a suitable calibration look-up table or calibration function determined for healthy patients having a full oxygen saturation level (e.g., SpOz=<NUM>%). A pulse (i.e. heart rate) can also be detected as the periodicity of intensity oscillations of the detected light.

However, the SpO<NUM> measurement (or equivalently, the value of the ratio R in the above example) can be adversely affected by stray light picked up by one or more of the light detectors (e.g., the non-central light detectors <NUM>-<NUM> and <NUM>-<NUM>). To improve robustness against stray light, the array of light sources <NUM> and the array of light detectors <NUM> are arranged as pairs. As shown in <FIG> and as labeled for exemplary light source <NUM>, the light sources <NUM>-<NUM> are each arranged as a pair of switched light sources, one light source 18R emitting red light and the other light source 18IR emitting IR light. The light sources <NUM>-<NUM> illuminate the corresponding light detector <NUM>-<NUM>. During an SpO<NUM> measurement, only a single IR/R light source/photodetector pair (e.g., the light source <NUM> and the light detector <NUM>) is used to measure the signal ratio R. However, the detectors of neighboring pairs (e.g., light detectors <NUM>-<NUM> and <NUM>-<NUM>) operate to detect any stray light. The signal R measured by the chosen pair can be corrected based on intensity values measured by the neighboring detectors (here indexed j) using the correction Rcorrected = R - κ where the correction κ is given by Equation (<NUM>): <MAT>.

In the correction κ, the index j runs over a set of detectors neighboring the pair (e.g., the light source <NUM> and the light detector <NUM>) used to measure signal R, the factor aj is a contribution factor for detector j (e.g., detectors closer to the edge of the array. (For example detectors <NUM>, <NUM>, <NUM>, as shown in <FIG>, receive more higher stray light compared to detectors <NUM>, <NUM>, <NUM>) are expected to detect higher stray light intensity and hence have higher α values), the factor βj is proportional to the Euclidean distance of the detector j to the pair used to measure signal R. The intensities Ist<NUM> and Ist<NUM> are measured without any of the light sources <NUM>-<NUM> operating for a given source detector <NUM>-<NUM> combination. The intensity Ist<NUM> corresponds to AC components of the intensity for the red light component of stray light observed by detector j, and similarly intensity Ist<NUM> corresponds to ac component of IR intensity component of stray light observed by detector j.

In other embodiments, the electronic processor <NUM> is programmed to correct the red/infrared light intensity ratio based on the detected ambient light using a machine-learned (ML) model. The ML model is trained on historical oxygen saturation measurement values. For example, data can be collected for a healthy test subject having SpO<NUM>=<NUM>%, with a ground truth measurement acquired in complete darkness (e.g., placed in a dark room with no stray light present). Various intensity levels and spatial orientations of stray light can then be applied during SpO<NUM> measurements together with measurements by the other detectors with all light sources of the set of light sources <NUM> turned off. The ML model (which may, for example, be a support vector machine (SVM), a neural network, or so forth) is trained to receive these as inputs and to output κ values that correct the measurements to output the a priori known ground truth SpO<NUM>=<NUM>%.

With reference now to <FIG>, and with continuing reference to <FIG>, the oxygen saturation monitor <NUM> optionally further includes at least one motion sensor configured to measure movement of at least one of the first clamp portion <NUM> and the second clamp portion <NUM>. The electronic processor <NUM> is, in these embodiments, programmed to determine the oxygen saturation value based on the detected red light and infrared light, along with the detected movement.

The at least one motion sensor includes (i) an accelerometer <NUM> configured to measure displacement of at least one of the first clamp portion <NUM> and the second clamp portion <NUM>; and (ii) a gyroscope <NUM> configured to measure rotation of at least one of the first clamp portion and the second clamp portion. As shown in <FIG>, the accelerometer <NUM> is disposed on (and configured to measure displacement of) the first clamp portion <NUM>, and the gyroscope <NUM> is disposed on (and configured to measure rotation of) the second clamp portion <NUM>, although the opposite arrangement may be implemented. It should be noted that since the first and second clamp portions <NUM>, <NUM> are mechanically connected by the clamping mechanism <NUM>, it is expected that the first and second clamp portions <NUM>, <NUM> (together with the clamping mechanism <NUM>) will be displaced or rotated as a single rigid unit.

The accelerometer <NUM> is configured to measure movement (for example, lateral movement) data in three dimensions (e.g., along x-, y-, and z-axes) of the first clamp portion <NUM>. A first displacement value is determined by the electronic processor <NUM> from the movement measured data by the accelerometer <NUM>. The first displacement value is determined by Equation <NUM>: <MAT> where V is a sum of positions of the accelerometer <NUM> in x-, y-, and z- directions.

The gyroscope <NUM> is configured to measure movement (for example, rotational movement) data in three axes (e.g., along pitch-, roll-, and yaw-axes) of the second clamp portion <NUM>. A second displacement value is determined by the electronic processor <NUM> from the movement data measured by the gyroscope <NUM>. The second displacement value is determined by Equation <NUM>: <MAT> where <MAT> is rotational data along the roll axis of the gyroscope <NUM>. It will be appreciated that only movement along the roll axis of the gyroscope <NUM> (e.g., rotation of the finger F in a clockwise/clockwise direction) is collected, as the finger would not rotate along a pitch axis or a yaw axis of the gyroscope, which are transverse to the roll axis. In determining the oxygen saturation value, the electronic processor <NUM> is programmed to determine a final displacement value by summing the first displacement value (e.g., from the data collected by the accelerometer <NUM> according to Equation <NUM>) and the second displacement value (e.g., from the data collected by the gyroscope <NUM> according to Equation <NUM>).

In other embodiments, the electronic processor <NUM> is programmed to determine the displacement values using a machine-learned (ML) model. The ML model is trained on historical oxygen saturation measurement values with displacement values compensated for. For example, data can be collected for a healthy test subject having SpOz=<NUM>%, with a ground truth measurement acquired with the monitor completely immobile. Various displacement and/or rotation motions can then be applied during SpO<NUM> measurements together with measurements by the accelerometer and gyroscope. The ML model, which may for example be a SVM, a neural network, or so forth, is trained to receive these as inputs and to output motion corrections that correct the measurements to output the a priori known ground truth SpO<NUM>=<NUM>%.

It will also be appreciated that the motion sensors <NUM>, <NUM> can be used in conjunction with the ambient light correction in various ways. For example, to reduce computational load, the ambient light correction factors κ can be computed only intermittently. This is based on the expectation that the ambient light is not expected to change except when accompanied by motion of the oxygen saturation monitor <NUM>. For example, the ambient light as seen by the monitor <NUM> may change any time the monitor <NUM> is moved or rotated, since in such a case the position and/or orientation of the monitor <NUM> relative to the bedside lamp or other ambient light source(s) may change. On the other hand, as long as the monitor <NUM> is stationary, the ambient light that is "seen" by the monitor <NUM> is unlikely to change rapidly. Even in the case of the bedside lamp being turned off, e.g. at lights-out, this will often be accompanied by some motion of the patient. Hence, in some contemplated embodiments, the ambient light correction κ is re-measured and re-computed relatively infrequently, e.g. at three minute intervals, but a detected movement of the monitor <NUM> will trigger an immediate re-measurement and re-computation of κ.

Referring back to <FIG>, the oxygen saturation monitor <NUM> also includes (or is controlled by) a computing device <NUM> (e.g., typically a workstation computer, or more generally a computer, although another form factor such as a tablet, a smartphone, and so forth is also contemplated). The workstation <NUM> comprises a computer or other electronic data processing device with typical components, such as the at least one electronic processor <NUM> (which can be alternatively be embedded in the clamp <NUM>), at least one user input device (e.g., a mouse, a keyboard, a trackball, and/or the like) <NUM>, and a display device <NUM>. In some embodiments, the display device <NUM> can be a separate component from the computer <NUM>.

One or more non-transitory storage media <NUM> are also provided to store data and instructions (e.g. software) that are readable and executable by the computing device <NUM> to perform oxygen saturation value measurement processes as disclosed herein, and/or executable by the workstation or other controller <NUM> to control the oxygen saturation monitor <NUM> to measure the oxygen saturation values (e.g., by determining and using the final displacement value and the corrected red/infrared light intensity ratio as described above). The non-transitory storage media <NUM> may, by way of non-limiting illustrative example, include one or more of a magnetic disk, RAID, or other magnetic storage medium; a solid-state drive, flash drive, electronically erasable read-only memory (EEROM) or other electronic memory; an optical disk or other optical storage; various combinations thereof; or so forth. The storage media <NUM> may comprise a plurality of different media, optionally of different types, and may be variously distributed. The storage media <NUM> can store instructions executable by the electronic processor <NUM> to perform an oxygen saturation value determination method or process <NUM>. From the final displacement value and the corrected red/infrared light intensity ratio, the electronic processor <NUM> is programmed to determine the oxygen saturation value using oxygen saturation value determination method.

With reference to <FIG>, an illustrative embodiment of the oxygen saturation method <NUM> is diagrammatically shown as a flowchart. At <NUM>, when the clamp <NUM> is affixed to the patient, the electronic processor <NUM> is programmed to control the central light source/detector pair (e.g., the light source <NUM> and the light detector <NUM>) to measure red and IR light, while the remaining light source/detector pairs are controlled to measure ambient light.

At <NUM>, the electronic processor <NUM> is programmed to correct the measured red and IR light data by subtracting the ambient light contribution from the measured light to generate corrected oxygen saturation values. This correction can be performed by the electronic processor <NUM> using Equation <NUM>. In some examples, the corrected oxygen saturation values can be displayed on the display device <NUM> of the computing device <NUM>.

At <NUM>, the electronic processor <NUM> is programmed to control the accelerometer <NUM> and the gyroscope <NUM> to measure the respective lateral movement and rotational movement data. It will be appreciated that operation <NUM> can be performed before, after, or simultaneously with operation <NUM> (i.e., the detection of light).

At <NUM>, the electronic processor <NUM> is programmed to compute the final displacement value from the motion data measured by the accelerometer <NUM> and the gyroscope <NUM>. With the final displacement value, the electronic processor is programmed to compute a displacement of the clamp <NUM> on the patient. For example, the original location of the clamp <NUM> (at operation <NUM>) can be calibrated to have Cartesian coordinates of (<NUM>,<NUM>,<NUM>). The displacement coordinates can be computed as (δt1, δt2, δt3).

At <NUM>, the electronic processor <NUM> is programmed to map the displacement coordinates (δt1, δt2, δt3) to a best possible light source/light detector pair that corresponds to the same anatomical area (e.g., where the clamp <NUM> is attached) as originally measured. The "best" light source/light detector pair is the pair that detects the least amount of ambient light (and therefore detects the most amount of red and/or IR light) determined using Equation <NUM>. To do so, the electronic processor <NUM> is programmed to determine new α and β values of the detectors <NUM>-<NUM> from Equation <NUM> to measure ambient light from the mapped displacement coordinates (δt1, δt2, δt3). For example, movement of the clamp <NUM> relative to the patient area which the clamp is attached may cause a different weight (e.g., α and/or β) for one of the light detectors <NUM>-<NUM>. In one example, the light source/detector pair <NUM>/<NUM> is used to record SpO<NUM> values. A clock-wise rotational motion of the finger F causes a similar movement of the clamp <NUM>, which is detected by the gyroscope <NUM>. This detected movement can trigger the electronic processor <NUM> to determine that new source/detector pair (e.g., light source/detector pair <NUM>/<NUM>) should be that maps to corresponding same anatomical area of the finger F that is used to measure SpO2 values before motion (e.g., the portion of the finger covered by the source/detector pair <NUM>/<NUM>). This detected movement of the finger F causes a change in the layout of the array of light sources <NUM> and the array of light detectors <NUM>, which requires for the electronic processor <NUM> to calculate new α and β values for all detectors. With the new calculations, for example, detector <NUM> will have new α and β values that is similar to what detector <NUM> had before the detected rotational motion as detector <NUM> is closer to new source/detector pair <NUM>, on a similar line, all other detector weightage can be computed for each light source/detector pair <NUM>-<NUM>/<NUM>-<NUM>.

In another example, the light source/detector pair <NUM>/<NUM> is again used to record SpO<NUM> values. The α value of the detector <NUM> is high and its β value is low due to its proximity to detector <NUM>. If the patient adjusts the clamp <NUM> towards the wrist (e.g., by sliding the clamp along the finger F), this translational movement is detected by the accelerometer <NUM>. The source/detector pair <NUM>/<NUM> begins to cover the same anatomical area of the finger F previously covered by the source/detector pair <NUM>/<NUM>. The electronic processor <NUM> determines the new α and β values for all detectors <NUM> to determine that the source/detector pair <NUM>/<NUM> should be used to measure SpO<NUM> values.

At <NUM>, the electronic processor <NUM> is programmed to use the new set of light sensors of the array of light sources <NUM> to mark this new set as a new light source/detector pair <NUM>/<NUM> to detect red and IR light signals to determine the oxygen saturation value in the patient.

Claim 1:
An oxygen saturation monitor (<NUM>), comprising:
a clamp (<NUM>) having opposing first (<NUM>) and second (<NUM>) clamp portions;
an array of light sources (<NUM>) disposed on the first clamp portion, each light source being switchable between (i) off, (ii) emitting red light, (iii) emitting infrared light; and (iv) emitting both red light and infrared light;
an array of light detectors (<NUM>) disposed on the second clamp portion facing the array of light sources, wherein each light detector of the array of light detectors is aligned to detect light emitted from a single one of the light sources and each light source is arranged to illuminate only a single one of the light detectors, thereby forming an array of light source / light detector pairs, wherein, for each light source / light detector pair, the light source corresponds to the light detector; and
an electronic processor (<NUM>) programmed to:
control the array of light sources (<NUM>) to emit switched red and infrared light by a single active light source (<NUM>-<NUM>) of the array of light sources with all other light sources of the array of light sources being off;
detect the switched red and infrared light using the light detector (<NUM>-<NUM>) of the array of light detectors (<NUM>) that is in the light source / light detector pair for the single active light source and is therefore aligned to detect emitted light from the single active light source; and
detect ambient light using the light detectors (<NUM>-<NUM>) of the array of light detectors other than the light detector that is aligned to detect emitted light from the single active light source.