Footsmart mat

Abstract

A system for predicting an occurrence of a foot ulcer includes a mat configured to be stood upon by a human subject, a plurality of sensor arrays disposed on or in said mat and arranged in adjacent proximity to one another. Each sensor includes an oxygenation probe, itself including a first light source and a light detector, and a secondary probe operable to utilize the light detector of the oxygenation probe and itself including a plurality of light sources exclusive of the first light source. The plurality of light sources of the secondary probe are arranged in a pattern around the oxygenation probe. The oxygenation probe is located at the approximate geometric center of the pattern. The system further includes a control module in signal communication with the light detector, and configured to independently control emission of light from the first light source of the oxygenation probe and the plurality of light sources of the secondary probe.

Claims

1. A system for predicting an occurrence of a foot ulcer, comprising: a mat configured to be stood upon by a human subject; a plurality of sensor arrays disposed on or in said mat and arranged in adjacent proximity to one another, each sensor comprising: an oxygenation probe comprising a first light source and a light detector; a secondary probe operable to utilize said light detector of said oxygenation probe and comprising a plurality of light sources exclusive of said first light source, said plurality of light sources being arranged in a pattern; wherein said oxygenation probe is located at the approximate geometric center of said pattern; and a control module in signal communication with said light detector, and configured to independently control emission of light from said first light source of said oxygenation probe and said plurality of light sources of said secondary probe.

2. The system of claim 1, wherein said light detector is configured to measure an amount of light that propagates from at least one of said plurality of light sources of said secondary probe, through a region of foot tissue of said human subject, to said light detector.

3. The system of claim 1, wherein said plurality of sensor arrays are disposed and arranged on a planar surface.

4. The system of claim 1, wherein each of said first light source, and each of said light sources of said secondary probe are configured to emit light perpendicular to said planar surface.

5. The system of claim 1, wherein said planar surface is configured to receive a bottom surface of a human foot, or to be placed on a bottom surface of a human foot.

6. The system of claim 1, wherein said secondary probe comprises between four and 10 of said light sources.

7. The system of claim 6, wherein said light sources of said secondary probe are arranged in a square or circle around said oxygenation probe.

8. The system of claim 1, further comprising an inertial measurement unit, a temperature sensor, and a pressure sensor in signal communication with said control module and disposed on or in said mat.

9. The system of claim 1, wherein said oxygenation probe comprises an area of about one centimeter.

10. The system of claim 1, wherein said plurality of light sources of said secondary probe are located about one centimeter from said oxygenation probe.

11. The system of claim 1, wherein said light sources of said secondary array are configured to emit light in the near infrared portion of the electromagnetic spectrum.

12. The system of claim 11, wherein said light sources of said secondary array are configured to emit at least two different wavelengths of light.

13. The system of claim 12, wherein a first wavelength is 730 nm and a second wavelength is 850 nm.

14. The system of claim 1, further comprising a computer processor in signal communication with an analysis module, a memory and an input/output module, wherein said input/output module is in signal communication with said plurality of sensor arrays.

15. The system of claim 14, wherein said analysis module is configured to differentiate ulcerous foot tissue from surrounding healthy foot tissue.

16. A method for predicting an occurrence of a diabetic foot ulcer, comprising: providing the system of claim 1; receiving the bottom portion of said human subject's foot upon said mat; generating a map of measured oxygenation on the plantar, mid-foot or heel region of said foot utilizing the system of claim 1; identifying, from said map, target regions of potential ulceration in said foot measured by said plurality of oxygenation probes; and interrogating said target regions of potential ulceration by generating a map of oxyhemoglobin within said foot utilizing said secondary probes.

17. The method of claim 16, further comprising determining an estimated difference index in oxyhemoglobin concentration between an area probed by said oxygenation probe and an area probed by said secondary probe.

18. The method of claim 17, wherein: if the estimated difference index is a positive value, an area of inflammation or hyperperfusion is identified; or if the estimated difference index is a negative value, an ischemic or hypervascularization condition is identified.

19. The method of claim 17, wherein said system further comprises a plurality of temperature sensors, and wherein said temperature sensors are utilized to determine regions of temperature asymmetry between the feet of said human subject.

20. The method of claim 19, wherein if a region of temperature asymmetry is determined, utilizing said region as an initial target for generating said map of oxyhemoglobin within said foot.

Description

DESCRIPTION OF DRAWINGS

(1) The present embodiments are illustrated by way of the figures of the accompanying drawings, which may not necessarily be to scale, in which like references indicate similar elements, and in which:

(2) FIG. 1 illustrates exemplary circuitry and LED controls of a system for predicting an occurrence of a foot ulcer, according to one embodiment;

(3) FIG. 2 shows a sensor board layout with an analog front end according to one embodiment;

(4) FIG. 3 shows an exemplary analog front end integrated circuit, according to one embodiment;

(5) FIG. 4 illustrates a FootSmart Mat concept according to one embodiment;

(6) FIG. 5 illustrates light propagation through a medium, according to one embodiment;

(7) FIG. 6 shows NIRS algorithms for quantifying changes in HbO.sub.2 and Hb according to one embodiment;

(8) FIG. 7 shows an exemplary light-tissue interaction model;

(9) FIG. 8 illustrates a system (FootSmart Mat′) for measuring and quantifying hemoglobin biomarkers of HbO.sub.2 and StO.sub.2 associated with oxygen delivery, according to one embodiment;

(10) FIG. 9 shows an exemplary sensor of the system, according to one embodiment;

(11) FIG. 10 illustrates an exemplary map layout according to one embodiment;

(12) FIG. 11 illustrates a Three-Zone vector for inflammation detection;

(13) FIGS. 12 and 13 show exemplary occlusion test results obtained by the FootSmart Mat system; and

(14) FIG. 14 illustrates a use of the FootSmart Mat system to determine an oxyhemoglobin vector.

DETAILED DESCRIPTION OF ILLUSTRATIVE EMBODIMENTS

(15) FIG. 1 illustrates exemplary circuitry and LED controls of a system for predicting an occurrence of a foot ulcer (colloquially termed a ‘FootSmart Mat’). In this embodiment, the diagram features a microcontroller unit (MCU) circuit board to control the data acquisition process and a sensor daughter board. The sensor board is electrically connected to the MCU board via a flex circuit cable to provide sensor commands and acquire optical sensor data. The MCU board communicates with the sensor daughter board via the serial peripheral bus (SPI). FIG. 2 shows the sensor board layout with the analog front end (AFE). The sensor board has an analog front end (AFE) IC, inertial measurement unit (IMU), two near infrared LEDS, temperature sensor, pressure sensor and photodiodes. An exemplary AFE IC is shown in FIG. 3.

(16) The AFE features a two-channel data acquisition system, programmable LED driver (four full scale ranges, 32, 64, 93, and 124 ma) to drive the two LEDs (i.e. 730 and 850 nm), two optical readout channels (two photodiode interface), first-in-first out (FIFO) memory, and two 19-bit A/Ds. The MCU board contains the microcontroller IC to acquire the data, a wireless Bluetooth interface for user interface support, built-in read only (ROM) and random-access (RAM) memory and battery management. The optical channel has 4 full scale ranges. These ranges are 4 to 32 μA. It has dual LED drivers, two photodiodes to capture the near infrared light, and SPI bus interface.

(17) FIG. 4 illustrates a FootSmart Mat concept according to one embodiment. A 730 nm LED (red, far left) is shown projecting light into a lightpipe which transmits the light and focuses it into a subject's foot. A second 850 nm LED (red, far right) is also shown with its lightpipe, and a photodiode is located between the two LEDs (blue, center). The red collar shown around each LED holds the lightpipe in place and is mounted on the sensor board. The blue color collar retains the lightpipe for the photodetector. The LEDs and photodiode will be organized as a sensor array to measure hemoglobin biomarkers HbO.sub.2 and StO.sub.2.

(18) Lightpipes can be fabricated with, e.g., acrylic, polycarbonate or Pyrex. Polycarbonate is stronger with higher impact resistance but is susceptible to scratching. Acrylic offers the benefits of ease of fabrication (i.e. cutting, polishing to remove scratches), while Pyrex is has the highest transmittance (94-95% vs. 90% for Acrylic).

(19) Referring now to FIG. 5, without wishing to be bound by theory, it is postulated based on known research that near infrared light projected into foot tissue will propagate in a semi-arcuate path, illustrated by the blue and green zones. The Beer-Lambert law (hereinafter the law′) predicts a linear relationship between absorbance (transmittance) of NIRS light and measuring the concentration of oxyhemoglobin. The molar extinction coefficient (c) is a measure of how strongly oxyhemoglobin absorbs light at a particular wavelength in units of M.sup.−1 cm.sup.−1 where the optical path length is in centimeters. The law defines the depth of penetration to be one-half the distance between the LED and photodetector. Effective penetration of light is also determined by several other factors: wavelength of light, attenuation coefficient (scattering, refraction, and absorption), area of irradiance (power density-watts/cm.sup.2).

(20) The NIRS algorithms for quantifying changes in HbO.sub.2 and Hb is shown FIG. 6 in equation 1.1 and 1.2 therein. I.sup.S(λx) is the intensity of light at wavelength ‘x’ during transmission. I.sup.b(λx) is the measure of light during baseline (with no light transmission) or the ambient light. ε.sub.oxy(λx) is the extinction coefficient for HbO.sub.2 at wavelength ‘x’ and ε.sub.deoxy(λx) is the extinction coefficient for Hb at wavelength ‘x’. L is the optical path length between the LED and photodetector. The oxygenation saturation (%) is calculated as: (HbO.sub.2/HbO.sub.2+Hb)×100. The light pipe provides effective flux coupling projecting the light with minimum flux loss. The losses include LED insertion (Fresnel) loss (up to 4% loss,) light leakage out the pipe wall (10% loss), and pipe exit Fresnel loss (4%). The radiation pattern at the pipe exit can be designed to maximize on-axis intensity and a narrow radiation pattern with a small viewing angle.

(21) In this embodiment, a dual wavelength bi-color LED is used. It features peak wavelength operation at 730 nm and 850 nm. Its radiated power is 24 mw at 50 ma and 230-360 mw of pulsed power output. It is packaged in a small surface mount package. The LED has a wide radiation field of +/−62 degrees to provide the best flux capture. A PIN photodiode (Vishay Semi VEMD5060X01) has been selected, is packaged as a surface mount device with a 7.5 mm.sup.2 sensitive area. It has a high responsivity of 64 mV/(microwatt/cm2).

(22) Without wishing to be bound by theory, a proposed light-tissue interaction model is shown in FIG. 7. In this embodiment, the LED emits near infrared light in the lightpipe and projects it into the tissue of the foot. The light is absorbed, scattered and reflected back into a second light pipe, and detected by the photodiode. An in-house bench test optical power analysis indicates that an LED operating at 124 ma (310 mW) can project 1,150 mw/cm.sup.2 power output at the lightpipe output. It was determined that 0.791 mw/cm2 of optical power can be available at the photodiode detector, which was estimated to produce 19.0 μA of output current.

(23) Loss of light through a living human hand (mid-palm penetration of 25 mm at 830 nm, Omnilux New-U low-level planar array light therapy source, 500 mW) have been measured previously at a rate of 99.99%. The average thickness of skin on the bottom of the foot is 1.5 mm This indicates a NIR penetration level of 2 mm should be adequate to detect any recurring foot ulcer with an average skin thickness of 1.5 mm. Thicker penetration depths may be required due to wound formation into subcutaneous tissue which will reduce optical power.

(24) Referring now to FIG. 8, a system (FootSmart Mat′) for measuring and quantifying hemoglobin biomarkers of HbO.sub.2 and StO.sub.2 associated with oxygen delivery is shown according to one embodiment. In this embodiment, the mat will also have integrated temperature sensors to detect temperature asymmetry between both feet.

(25) In this embodiment, In this embodiment, the target area is about 1.0 cm in diameter, a typical size of a DFU. In the center of the sensor array (the target area) an LED pair and photodiode, cooperatively “an oxygenation probe”, is located adjacent of each other.

(26) A set of NIRS sensor arrays will generate oxyhemoglobin (HbO.sub.2) and tissue oxygen saturation (StO.sub.2) maps. Each sensor array can have a number of sensor pairs, e.g., 4, 5, 6, 7, 8, 9, 10 pairs; in this example, the system has 8 LED pairs that emit light at 730 nm and 850 nm and are arranged in a ring outside the recurring ulcer target area as shown in FIG. 9. As used herein, the LED pairs (8, in this example), and the photodiode of the oxygenation probe, are collectively referred to as a “secondary probe.”

(27) In one embodiment, a measurement of oxygenation includes first measuring HbO.sub.2 and Hb in the target area using the oxygenation probe. The LEDs in the outer ring of the array will then be sampled capturing adjacent region data around the target area (i.e., using the secondary probe).

(28) In doing so, infrared light is projected through each dedicated lightpipe into the foot tissue, and captured by the photodiode in the target area as shown in FIG. 9. This method will generate a map of oxyhemoglobin. The map layout is illustrated in FIG. 10 with the target area in the center and LEDs surrounding the target area. The inner rim of the adjacent region will be 1 cm from the outer rim of the target region. The radius of the outer rim of the adjacent region has been chosen such that the surface area of each of the eight segments are the same as the target area and equal to 0.79 cm.sup.2.

(29) The estimated difference (ED) index in oxyhemoglobin concentration (O) between the target (T) and the adjacent regions are defined as: ED=OT−OA where OT is the oxyhemoglobin in the target area and OA is the oxyhemoglobin in the adjacent area. If the ED index is a positive value, this may indicate inflammation (i.e. indicating hyperperfusion) exists between the target area and adjacent regions. If the ED index is a negative value, an ischemic condition may exist with hypervascularization occurring in the recurring ulcer site.

(30) In addition, it has been determined that a predictive vector of inflammation or ischemia can be generated by adding the oxyhemoglobin values in adjacent regions. For example, FIG. 11 illustrates a Three-Zone vector for inflammation detection by adding values for each adjacent region (C1, C7, and C8) or ED=OT−(OC1+OC7+OC8). One, two, three, or four zone vectors can be computed. The adjacent area with the highest value in the group, or a weighted sum of the group can determine the direction of the predictive vector.

(31) Exemplary occlusion test results are shown in FIGS. 12 and 13 for HbO.sub.2 and Hb plots respectively. Two 240-second (i.e. 4-minute) sequential cycles are shown. Each cycle has a 120 second baseline period (no occlusion, sitting at rest) followed by a 60 second occlusion period (160 mmHg applied pressure) and a 60 second recovery period (occlusion cuff pressure is released). The analysis indicates clear indication of HbO.sub.2 measurement with an oxygen demand (i.e. extraction) event (i.e. HbO.sub.2 decrease) shown after occlusion pressure is applied as indicated by a negative slope output (i.e. 120 and 420 seconds) and an oxygen supply event (i.e. HbO.sub.2 supply) shown after occlusion pressure is removed (i.e. positive slope output—180 and 480 seconds).

(32) The data clearly show the loss and recovery of oxyhemoglobin as a two-step process. The Hb measurement shows a similar response except a positive slope measurement due to application of occlusion pressure. These data indicate several advantages (of many) of the present system and method: 1) it is sensitive enough to track oxygen supply/demand (extraction); 2) a wide dynamic range of the system is 96 dB (16-bit resolution) is demonstrated; 3) the responsivity (i.e. input-output gain) of the photodetector system is adequate to detect the hemoglobin biomarkers for the diabetic subject.

(33) An occlusion test on a type 2 diabetic human subject with has revealed that it is possible with the system disclosed to detect and measure oxyhemoglobin in the plantar region.

(34) Referring now to FIG. 14, in one embodiment, each sensor can be used to determine an oxyhemoglobin vector, which can be used as an interpretive tool for determining physiological pathways of inflammation or ischemia. For example, the two, three, four and single zones depicted in FIG. 14 can be correlated to oxygen flow in the periwound of an ulcer from a particular direction. A flood zone, in comparison can correlate with oxygen flow being directed to the center of the ulcer.

(35) A number of illustrative embodiments have been described. Nevertheless, it will be understood that various modifications may be made without departing from the spirit and scope of the various embodiments presented herein. For example, while the present disclosure has primarily focused on predicting the occurrence of foot ulcers, the same systems and methods can be adapted for predicting pressure ulcers elsewhere on the body, including but not limited to the heel, tailbone, hips or ankles. Accordingly, other embodiments are within the scope of the following claims.