Device and method suitable for monitoring arterial blood in a body part

Abstract

A device comprising a piece of planar substrate embedded with two sensors and two emitters. The substrate has a generally planar surface for application onto the wearer's body part. The emitters and sensors are shown to be arranged in such a way that no subset of any two emitters and one sensor, or subset of any two emitters and one sensor, forms a straight line, which prevents the two sensors from detecting the same noise caused by the same wearer movements.

Claims

1. A wearable device suitable for monitoring blood in a body part, comprising a substrate suitable for being placed on the body part, the substrate attached with at least two light emitters, and at least two light sensors; the substrate comprising a microprocessor for the operation of the emitters and light sensors the at least two light emitters arranged such that light from each of the at least two light emitters is capable of diffusing through the body part to arrive at each of the at least two light sensors; the substrate being capable of substantially holding the at least two light emitters and at least two light sensors; such that the at least two light emitters and at least two light sensors generally form a plane for being applied to a surface on one side of the body part; the at least two light emitters capable of operating sequentially to emit light to be detected by the sensors; and the at least two light sensors having positions such that each of the at least two light sensors detects light from every one of the at least two light emitters in a different direction; wherein the substrate is flexible.

2. A wearable device suitable for monitoring blood in a body part, as claimed in claim 1, wherein the at least two sensors operate to sequentially detect light.

3. A wearable device suitable for monitoring blood in a body part, as claimed in claim 1, wherein the substrate is a flexible fabric, and the substrate is capable of arranging the at least two light emitters and at least two light sensors in the plane.

4. A wearable device suitable for monitoring blood in a body part, as claimed in claim 1, wherein the substrate is a flexible plastic, and the substrate is capable of arranging the at least two light emitters and at least two light sensors in the plane.

5. A wearable device suitable for monitoring blood in a body part, as claimed in claim 1, wherein the substrate is provided with an adhesive surface for adhering to the skin of the wearer.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) It will be convenient to further describe the present invention with respect to the accompanying drawings that illustrate possible arrangements of the invention, in which like integers refer to like parts. Other embodiments of the invention are possible, and consequently the particularity of the accompanying drawings is not to be understood as superseding the generality of the preceding description of the invention.

(2) FIG. 1 is an illustration of a first embodiment of the invention;

(3) FIG. 2 is a schematic diagram of the internal arrangement of the embodiment of FIG. 1;

(4) FIG. 3 is a schematic diagram of the internal arrangement of the embodiment of FIG. 1;

(5) FIG. 4 is a chart showing noise signals which can be treated by the embodiment of FIG. 1;

(6) FIG. 5 is a diagram explaining the effects of noise components which can be treated by the embodiment of FIG. 1;

(7) FIG. 6 is a chart showing heart rate and noise motions which can be treated by the embodiment of FIG. 1;

(8) FIG. 7 further explains the noise component discussed for FIG. 5;

(9) FIG. 8 shows a second embodiment to the invention;

(10) FIG. 9 further shows the second embodiment of FIG. 8;

(11) FIG. 10 further shows the second embodiment of FIG. 8;

(12) FIG. 11 further shows the second embodiment of FIG. 8;

(13) FIG. 12 explains the workings of the embodiment of FIG. 8;

(14) FIG. 13 explains an advantage in the embodiment of FIG. 8;

(15) FIG. 14 shows yet a further embodiment of the invention;

(16) FIG. 15 shows yet a further embodiment of the invention;

(17) FIG. 16 further shows the second embodiment of FIG. 15;

(18) FIG. 17 shows yet a further embodiment of the invention;

(19) FIG. 18 shows yet a further embodiment of the invention;

(20) FIG. 19 shows yet a further embodiment of the invention;

(21) FIG. 20 shows yet a further embodiment of the invention;

(22) FIG. 21 shows yet a further embodiment of the invention;

(23) FIG. 22 shows the embodiment of FIG. 21 in use;

(24) FIG. 23 shows how the embodiment of FIG. 21 may be made;

(25) FIG. 24 shows how the embodiment of FIG. 21 may operate;

(26) FIG. 25 shows how the embodiment of FIG. 21 may operate;

(27) FIG. 26 shows how the embodiment of FIG. 21 may operate;

(28) FIG. 27 a variation of the embodiment of FIG. 21; and

(29) FIG. 28 a variation of the embodiment of FIG. 21;

(30) FIG. 29 shows yet a further embodiment of the invention;

(31) FIG. 30 shows how the emitter in the embodiment of FIG. 29 operates;

(32) FIG. 31 also shows how the emitter in the embodiment of FIG. 29 operates;

(33) FIG. 32 also shows how the emitter in the embodiment of FIG. 29 operates;

(34) FIG. 33 also shows how the emitter in the embodiment of FIG. 29 operates; and

(35) FIG. 34 illustrates a heartbeat signal read by the embodiment of FIG. 29.

DESCRIPTION OF EXEMPLARY EMBODIMENTS

(36) FIG. 1 shows a first embodiment 100, comprising a ring 102 which is a heart rate monitor. The ring can be worn on the finger of a person whose heart rate is to be monitored during exercise. The finger is not illustrated in the drawing.

(37) The ring 102 is installed with two emitter-and-sensor 106 pairs. Therefore, there are two emitters 104 and two sensors 106 in total. A suitable housing 108 is attached to the ring 102 for containing a microprocessor and memory required for operating the emitters 104 and sensors 106, and for manipulating infrared signal data as detected by the sensors 106.

(38) Typically, the emitters 104 are Light Emitting Diodes or LEDs which emit light that is absorbable by blood, such as infrared. In other embodiments however, any other suitable frequency can be used including visible red, green or blue light, or any combination thereof.

(39) The two emitters 104 are provided in the ring 102 such that they are at opposite sides of the wearer's finger when the ring 102 is worn. The two sensors 106 are also provided such that they are at opposite sides of the finger when the ring is worn but also to be at about 90 degrees to an imaginary line drawn through the emitters 104. The positions of both sensors 106 allows each sensor 106 to be capable of detecting light projected into the finger by both emitters 104.

(40) FIG. 2 is a schematic diagram of the arrangement of the two emitters 104 and two sensors 106 in the ring 102. Due to the small radius of the ring 102, light emitted by the emitters 104 need not be projected directly at the sensors 106. Instead, the sensors 106 merely needs to detect infrared light scattered through or reflected by tissues and blood in the finger. Other ways of arranging the emitters 104 and the sensors 106 are possible as long as each emitter 104 is placed a distance away from both of the sensors 106, such that a sufficiently long transmission path through the finger is provided for absorption of infrared light by blood.

(41) The microprocessor operates the emitters 104 such that they emit infrared light one after the other. Thus, both sensors 106 first detect infrared light scattered through the finger from one emitter 104, and then detect infrared light scattered through the finger from the other emitter 104.

(42) As illustrated in FIG. 2 and FIG. 3, transmission paths P11 and P12 are observed by sensors S1 and S2 respectively when emitter L1 emits infrared light into the finger. The infrared signals observed by both sensors S1 and S2 are then recorded for processing by the microprocessor. Subsequently, the microprocessor instructs emitter L1 to stop emitting infrared light and instructs emitter L2 to start emitting infrared light. Both sensors S1 and S2 then detect the infrared signals via transmission paths P21 and P22, respectively.

(43) Accordingly, four transmission paths through the finger P11, P12, P21, P22 are monitored in this embodiment. Four sets of data are observed using only two sensors 106 and two emitters 104. In contrast, the prior art requires three emitters and three sensors to obtain just three observations. Advantageously, the present embodiment requires less hardware while making a greater number of observations than devices of the prior art.

(44) Typically, the sensors can detect fluctuating infrared transmissions through the finger which are attributed to heartbeat. Skin, tissue, venous blood, and the blood are all capable of absorbing infrared light. However, the volume of arteries periodically increases and decreases with the pumping of the heart, giving rise to these fluctuating transmissions.

(45) FIG. 4 explains how these fluctuating transmissions come about. The vertical axis of the chart in FIG. 4 shows absorption of the infrared light. Together, the troughs form the base 302 of the waveform which is indicative of the amount of light absorbed by skin, tissues, venous blood, which are relatively constant, and when artery blood volume is smallest. The magnitude 300 between the troughs to the peaks is attributed to an increase of infrared absorption when the artery volume increases and is filled with blood.

(46) However, the infrared transmission signals detected by the sensor are subjected to noise when the wearer exercises. For example, the wearer's movements can cause continual small physical displacements of emitter and sensor positions. Furthermore, the cross-sectional area of the finger on which the ring is worn varies easily when the finger is flexed during exercise. All these movements vary the distance of the transmission paths through the finger, which introduce variations into the transmission signals as unwanted noise.

(47) In practice, only transmission path changes in the plane defined by the sensors 106 contribute noise. FIG. 5 illustrates the plane as an x-y plane. Muscle or tissue volume changes in the q-axis perpendicular to the x-y plane are relevant only if they cause the finger to expand or contract in the x-y plane, or if any vertical movements cause the ring 102 to slip along the finger which effectively moves the x-y plane along the finger length.

(48) FIG. 6 is a chart showing how the heart rate of a wearer is detected as a periodic signal and how the periodic heart rate signal can be overwhelmed by noise due to movements of the wearer. In about the first 10 seconds of the chart the wearer stays stationary and the signals representing heart rate are low in peak-to-peak amplitude because volumetric changes in the arteries tend to be relatively small.

(49) All periodic fluctuations in the infrared transmission signal can be attributed to arterial pulsation, and one set of observation obtained using one emitter and one sensor may even be enough to monitor the heart rate. The DC component in these 10 seconds is largely contributed by tissues, venous blood and other stable components in the wearer's finger, while the AC component is contributed by heartbeat.

(50) At 15 seconds in the chart, however, when the wearer starts to run, jump and or move his finger, the movements easily overshadow the heart rate signals with noise. That is, the AC component now include noise and fluctuates much higher and lower about the DC level and overshadows the AC component contributed by the heartbeat.

(51) The amount of light emitted by one of the emitters 104 and detected at any one of the sensors 106 can be approximately modelled as follows:
m(t)=L I.sub.0(t)(1+γ hb(t))(1+N.sub.s(t)+N.sub.f(t)+z(t)) where: m(t) is the signal received at any one of the IR sensors 106 L is constant gain of the IR sensor I.sub.0(t) is the transmitted signal to the IR emitter hb(t) is the heart rate signal γ is coupling coefficients of the heart rate signal hb(t) N.sub.s(t) is slow varying noise in the detected signals N.sub.f(t) is are typical additive thermal noise in the detected signals, and z(t) is noise signals due to movement caused by flexing of the body part.

(52) If N.sub.s(t)=0, N.sub.f(t)=0, z(t)=0, the infrared signals are proportional to periodic pumping of blood by the heart, i.e.
m(t)=L I.sub.0(t)(1+γ hb(t))

(53) If there is no noise in the infrared signals, the peaks in the waveform can be directly counted to obtain the heart rate of the wearer. However, if there is a lot of noise from wearer movement and z(t) becomes significant, then the infrared signals have to be mathematically treated to extract the heart rate signal from the noisy signal.

(54) FIG. 7 illustrates how movement signals z(t) in the x-y plane defined by the location of the sensors 106 can be re-written as:
z(t)=ε[h(t)cos(θ)+v(t)sin(θ)] where h(t) is the movement signal caused by flexing the finger in the wearer's horizontal direction; v(t) is movement signal caused by flexing the finger in the wearer's relative vertical direction; the direction of sensor k is θ from the horizontal direction; and ε is the coupling coefficient for the movement signal to the sensor.

(55) Movements affecting the infrared signals are mathematically determined for their effects within the x-y plane only. The x-y plane is defined by the sensors 106 and need not necessarily be ‘horizontal’ or parallel to the ground.

(56) In this embodiment, the four observations obtained from the two sensors 106 can be modelled as follows:
m.sub.1(t)=L.sub.1 I.sub.01(t)(1+γ.sub.1 hb(t))(1+N.sub.s1(t)+N.sub.f1(t)+z.sub.1(t))  (1)
m.sub.2(t)=L.sub.2 I.sub.02(t)(1+γ.sub.2 hb(t))(1+N.sub.s2(t)+N.sub.f2(t)+z.sub.2(t))  (2)
m.sub.3(t)=L.sub.3 I.sub.03(t)(1+γ.sub.3 hb(t))(1+N.sub.s3(t)+N.sub.f3(t)+z.sub.3(t))  (3)
m.sub.4(t)=L.sub.4 I.sub.04(t)(1+γ.sub.4 hb(t))(1+N.sub.s4(t)+N.sub.f4(t)+z.sub.4(t))  (4) Where: m(t), m.sub.2(t), m.sub.3(t), m.sub.4(t) are the signal received at the 4 sensors 106 respectively L.sub.1, L.sub.2, L.sub.3, L.sub.4 are constant gain of each IR sensors 106 I.sub.01(t), I.sub.02(t), I.sub.03(t), I.sub.04(t) are the transmitted signal to the IR LED emitters 104 respectively hb(t) is the heart rate signal γ.sub.1, γ.sub.2, γ.sub.3, γ.sub.4 are coupling coefficients of the heart rate signal hb(t) N.sub.s1(t), N.sub.s2(t), N.sub.s3(t), N.sub.s4(t) are slow varying noise in the detected signals N.sub.f1(t), N.sub.f2(t), N.sub.f3(t), N.sub.f4(t) are typical additive thermal noise in the detected signals, and z.sub.1(t), z.sub.2(t), z.sub.3(t), z.sub.4(t) are noise signals due to movement.

(57) The movement noise signals z.sub.1(t), z.sub.2(t), z.sub.3(t), z.sub.4(t) can be re-written as:
z.sub.k(t)=ε.sub.k(h(t)cos(θ.sub.k)+v(t)sin(θ.sub.k)) where h(t) is the movement signal in the horizontal; v(t) is movement signal in the relative vertical direction; the direction of sensor 106 k is θ.sub.k from the horizontal direction; and ε.sub.k are coupling coefficients for the movement signal to the sensors 106.

(58) Assuming that both γ.sub.k, ε.sub.k are much smaller than 1, the infrared signals at each sensor can be represented as being composed of both DC and AC components, (m.sub.ack(t), m.sub.dck(t)).

(59) When the wearer first puts on the ring 102, he is requested by the microprocessor via a display (not shown) in the housing 108 to stay stationary without moving. At this stage, the infrared signals detected by the sensors 106 can be attributed to heart rate only. The raw data from each of the sensors 106 is firstly treated with a simple Finite Input Response (FIR) low pass filter to remove all high frequency signals. Subsequently, the slow drifting DC offset is removed using a filter or a moving window to extract the DC offset and subtract it from the signals. At this stage, if the microprocessor detects that the infrared signals read by the different sensors 106 differ greatly in amplitude, the gain of each of the four sensors 106 is adjusted until the difference in the amplitudes of the transmission signals fall within a pre-determined deviation. By this, the gain of each of the sensors are normalised, and equations (1) to (4) can then be approximated as:
m.sub.ac1(t)=hb(t)+N′.sub.s1(t)+N′.sub.f1(t)+z.sub.1′(t)  (1b)
m.sub.ac2(t)=hb(t)+N′.sub.s2(t)+N′.sub.f2(t)+z.sub.2′(t)  (2b)
m.sub.ac3(t)=hb(t)+N′.sub.s3(t)+N′.sub.f3(t)+z.sub.3′(t)  (3b)
m.sub.ac4(t)=hb(t)+N′.sub.s4(t)+N′.sub.f4(t)+z.sub.4′(t)  (4b) where N′.sub.sk(t), N′.sub.fk(t), z.sub.k′(t) are scaled versions of the original noise signals.

(60) After normalisation, the ring 102 can now be used to monitor heart rate. When there is no movement or a very small amount of movements, the deviation of the amplitudes of signals detected by the sensors remains at the normalised level. The maximum signal to noise ratio (SNR) of the heart rate signal can be obtained by adding up the normalised AC component input signal, i.e.
y(t)=m.sub.ac1(t)+m.sub.ac2(t)+m.sub.ac3(t)+m.sub.ac4(t)

(61) Effectively, the noise will be reduced as the signal is accentuated by the summation of the independent observations of each sensor.

(62) However, when the wearer exercises, noise signals z.sub.1′(t), z.sub.2′(t), z.sub.3′(t), z.sub.4′(t) dominate the signals detected by the sensors 106. The noise can then be treated by finding the column vector ŵ=[w.sub.1 w.sub.2 w.sub.3 w.sub.4].sup.T where

(63) $\hat{y}={\hat{w}}^{T}M;\mathrm{and}$$M=\left[\begin{array}{cc}{m}_{ac1}\left[0\right]m_{ac1}\left[1\right]\mathrm{.Math.}\mathrm{.Math.}{m}_{ac1}& \left[K-1\right]\\ m_{ac2}\left[0\right]m_{ac2}\left[1\right]\mathrm{.Math.}\mathrm{.Math.}{m}_{ac2}& \left[K-1\right]\\ m_{ac3}\left[0\right]m_{ac3}\left[1\right]\mathrm{.Math.}\mathrm{.Math.}{m}_{ac3}& \left[K-1\right]\\ m_{ac4}\left[0\right]m_{ac4}\left[1\right]\mathrm{.Math.}\mathrm{.Math.}{m}_{ac4}& \left[K-1\right]\end{array}\right];\mathrm{and}$$\hat{y}=\left[y\left[0\right]y\left[1\right]\mathrm{.Math.}y\left[k-1\right]\right]$

(64) and ŷ is a linear combination of input signal which maximizes:

(65) $\frac{{\hat{w}}^T\hat{s}{\hat{s}}^T\hat{w}}{{\hat{w}}_{mm}^{T_{\mathrm{.Math.}}}\hat{w}}$

(66) where .sub.mm is the cross correlation matrix of the 4 signals from movement. ŝ=[s.sub.1 s.sub.2 s.sub.3 s.sub.4].sup.T the corresponding gain of the heart rate signal, in this case when all the 4 input channels are normalized

(67) ŝ=[1 1 1 1].sup.T and .sub.mm=MM.sup.T−σ.sup.2ŝŝ.sup.T, where σ.sup.2 is the variance of the heart rate signal.

(68) As .sub.mm is positively defined, it can be written that

(69) ${\mathrm{.Math.}}_{mm}=R^{\frac{1}{2}}.Math.R^{\frac{1}{2}}$

(70) and it can be written that

(71) $\hat{u}=R^{\frac{1}{2}}\hat{w}$$\mathrm{and}$$\hat{w}=R^{-\frac{1}{2}}\hat{u}$

(72) Accordingly, the problem to be solved becomes:

(73) $\underset{\left|\right|\hat{u}\left|\right|}{\max }{\hat{u}}^T{R}^{\frac{1}{2}}\hat{s}.Math.{\hat{s}}^T{R}^{-\frac{1}{2}}\hat{u}$$\mathrm{or}$$\underset{\left|\right|\hat{u}\left|\right|}{\max }{\left({\hat{u}}^T{R}^{-\frac{1}{2}}\hat{s}\right)}^2$

(74) The expression is maximum when:

(75) $\hat{u}=R^{-\frac{1}{2}}\hat{s}\therefore \hat{w}=R^{-\frac{1}{2}}\left(R^{-\frac{1}{2}}\hat{s}\right)={\mathrm{.Math.}}_{mm}^{-1}\hat{s}$$\mathrm{where}{\mathrm{.Math.}}_{mm}={\mathrm{MM}}^T-{\sigma }^2\hat{s}{\hat{s}}^T$

(76) To remove movement noise, the four sets of observations obtained from the two sensors 106 are used. If the four signals detected in the four transmission paths are synchronous and in-phase, and if the amplitudes of all the four signals differ only within a signal standard deviation of σ, it may be taken that heartbeat signals dominate the infrared signals with little noise. The signals can simply be added up and the peaks in the signal waveform counted to determine heart rate.

(77) On the other hand, if noise dominates the infrared signals, the infrared signals will not be in phase and the amplitudes of all the four signals will differ beyond the standard deviation σ. In this case, to extract the heart rate signal, the correlation index across the four signals is calculated. That is, the covariance matrix of the signals calculated:
.sub.mm=MM.sup.T−σ.sup.2ŝŝ.sup.T.

(78) As mentioned earlier σ.sup.2ŝŝ.sup.T was obtained by calculating the standard deviation of the four input signals when there was no wearer movement. The four input signals are then normalised to standard deviations of σ, and σ.sup.2ŝŝ.sup.T becomes

(79) $\mathrm{\sigma 2}=\left[\begin{array}{c}1111\\ 1111\\ 1111\\ 1111\end{array}\right]$

(80) The vector can be calculated, where
w=.sub.mm.sup.−1ŝ where w is a 4×1 column vector: ŷ=ŵ.sup.TM y[n] is a linear combination of the 4 input signals

(81) At ŝ=[1 1 1 1].sup.T all four channels would be normalized.

(82) The above mathematical treatment normalises the signals received by the sensor such that the combined signals have the lowest total energy. Having the lowest total energy implies that the total amount of noise has been adjusted to be at the lowest and least influential.

(83) Furthermore, the independent observations of transmission signals due to heartbeat will be in phase with each other, differing only by a scaling factor. Therefore, if the infrared signals are summed up with some specific weight, the noise signals can be minimized and hence increasing the signal to noise ratio.

(84) Typically, the wearer's movements can be quite periodic when he is performing a repetitive exercise such as running. Nevertheless, these periodic exercise movements do not impart an identical and periodic noise to the sensor readings. This is because the several transmission paths through the finger between each pair of emitter and sensor are different, and it may be expected that unique noise is imposed on each sensor by the different local layers of wobbly tissue and other bodily components, even if the wearer's movements is periodic and applied to the device 100 as a whole. Accordingly, summation of the infrared signals detected by the different sensors will not add up to accentuate any identical periodic noise signals.

(85) To further improve signal to noise ratio, it is desirable to have more independent observations to increase observation diversity. FIG. 8 shows a second embodiment to this effect. FIG. 9 to FIG. 11 are schematics diagrams of the second embodiment of FIG. 8. The second embodiment comprises a ring 102 installed with three emitter-and-sensor pairs, instead of two. Each emitter 104 is placed immediately next to one of the sensors 106 and away from the other two sensors 106. In this way, each emitter 104 is able to project light to the two sensors 106 across the ring 102 and through the finger. Likewise, the sensor 106 immediately next to an emitter 104 is able to receive light from the two emitters 104 across the ring 102.

(86) In operation, the emitters L1, L2, L3 are switched on in consecutive order, one after another. When emitter L1 is ON, both sensors S1 and S2 detect light from emitter L1 in respective transmission paths P11 and P12. When L2 is ON, sensors S2 and S3 detect light from emitter L2 in respective transmission paths P22 and P23. When L3 is ON, sensors S1 and S3 detect light from emitter L2 in respective transmission paths P31 and P33.

(87) As with the first embodiment, in order to remove noise from wearer movements, the amplitudes of the six observations are normalized by calculating their variance or standard deviation. The detected signals are modelled as follows:
m.sub.1(t)=L.sub.1 I.sub.01(t)(1+γ.sub.1 hb(t))(1+N.sub.s1(t)+N.sub.f1(t)+z.sub.1(t))  (1a)
m.sub.2(t)=L.sub.2 I.sub.02(t)(1+γ.sub.2 hb(t))(1+N.sub.s2(t)+N.sub.f2(t)+z.sub.2(t))  (2a)
m.sub.3(t)=L.sub.3 I.sub.03(t)(1+γ.sub.3 hb(t))(1+N.sub.s3(t)+N.sub.f3(t)+z.sub.3(t))  (3a)
m.sub.4(t)=L.sub.4 I.sub.04(t)(1+γy.sub.4 hb(t))(1+N.sub.s4(t)+N.sub.f4(t)+z.sub.4(t))  (4a)
m.sub.5(t)=L.sub.5 I.sub.05(t)(1+γ.sub.5 hb(t))(1+N.sub.s5(t)+N.sub.f5(t)+z.sub.5(t))  (5a)
m.sub.6(t)=L.sub.6 I.sub.06(t)(1+γ.sub.6 hb(t))(1+N.sub.s6(t)+N.sub.f6(t)+z.sub.6(t))  (6a) Where: m(t), m.sub.2(t), m.sub.3(t), m.sub.4(t), m.sub.5(t), m.sub.6(t) are the signal received at the 6 sensors 106 respectively I.sub.01(t), I.sub.02(t), I.sub.03(t), I.sub.04(t), I.sub.05(t), I.sub.06(t) are the transmitted signal to the IR LED emitters 104 respectively L.sub.1, L.sub.2, L.sub.3, L.sub.4, L.sub.5, L.sub.6 are constant gain of each IR sensors 106 hb(t) is the heart rate signal γ.sub.1, γ.sub.2, γ.sub.3, γ.sub.4, γ.sub.5, γ.sub.6 are coupling coefficients of the heart rate signal hb(t) N.sub.s1(t), N.sub.s2(t), N.sub.s3(t), N.sub.s4(t), N.sub.s5(t), N.sub.s6(t) are slow varying noise in the detected signals N.sub.f1(t), N.sub.f2(t), N.sub.f3(t), N.sub.f4(t), N.sub.f5(t), N.sub.f6(t) are typical additive thermal noise in the detected signals, and z.sub.1(t), z.sub.2(t), z.sub.3(t), z.sub.4(t), z.sub.5(t), z.sub.6(t) are noise signals due to movement.

(88) The subsequent mathematical treatment for six sensors 106 is the same as that described for the first embodiment.

(89) FIG. 12 shows why although transmission paths P12 and P33 are practically the same physical path but the noise imposed onto the signals transmitted in paths P12 and P33 are not identical. This is because P12 and P33 are transmissions in opposite directions although the transmission transmits in virtually the same path 802 between the two sensor S2 and sensor S3. The random folds of skin on the finger and the different tissues under the skin provide an asymmetrical transmission path between sensor S2 and sensor S3. Therefore, the angle of infrared light incident on the skin from emitter L1 towards S2 is likely to be different from the angle of infrared light incident on the skin from emitter L3 towards S3. Similarly, the extent of reflection and penetration of the incident infrared light into the skin surface is different in the two different directions, as indicated by the arrows in FIG. 12. Thus, noise signals imposed on the sensors S2 and S3 due to movement and flexing of the finger are not identical in the different transmission directions. This explains why using the same physical transmission path for two sensors in different directions does not amount to replicating a same signal. This also explains why the wearer's periodic exercise movements do not impose periodic and identical noise signals on all the sensors even if wearer movements are periodic, as the different transmission directions ensures that the noise is unique in each sensor.

(90) In both embodiments, the use of one sensor 106 with two different emitters 104 increases the number of independent observations made with each sensor. In the first embodiment, only two emitters 104 and two sensors 106 are required for obtaining four observations. In the second embodiment, three sensors 106 and three emitters 104 provide six observations. This is advantageous over the prior art as less sensors or emitters is required for obtaining a greater number of observations.

(91) More advantageously, in the second embodiment, any one of the emitters 104 or the sensors 106 may break down and four observations are nevertheless obtainable. For example, temporarily failure situations may happen when ambient light shines directly into one of the sensors, saturating the sensor 106. FIG. 13 shows the ring of the second embodiment having three sensor and emitter pairs. Strong ambient light represented by the block arrow shines onto sensor S1 but is blocked by the wearer's finger over which the ring is worn from shining onto S2 and S3. When the sensor S1 is so exposed to ambient light, sensor S1 becomes saturated and unusable for detecting infrared transmission signals. However, as sensors S3 and S2 are blocked from the ambient light, sensors S3 and S2 remain functional. Thus, sensor S3 remains capable of reading infrared transmission signals from L2 and L3, and sensor S2 remains capable of reading infrared transmission signals from L1 and L2. The microprocessor can detect that sensor S1 is saturated and disregard the sensor S1, and use the remaining four observations provided by sensors S2 and S3 to determine the heart rate. As described, L1 and L2 takes turns to emit to the sensors S2 and S3 to provide the four observations. In contrast, an ambient light saturation of a sensor in a prior art device which uses three sensors to detect light from three respective, separate emitters will compromise the accuracy of the device because one observation becomes unusable.

(92) As a matter of choice, in the first embodiment, only three observations may be used to monitor heart rate from the two emitters 104 and two sensors 106, even though four observations are obtainable. Similarly, in the second embodiment, only three observations may be used even though the three sensors 106 and three emitters 104 provide the possibility of six observations, particularly where any two of such three observations is obtained using the same sensor 106.

(93) Accordingly, the embodiments described includes a device suitable for monitoring blood in a body part 100 comprising: a plurality of light emitters 104 at least one sensor 106, the plurality of light emitters 104 arranged such that light from the plurality of light emitters 104 is capable of passing through a body part to arrive at the least one sensor 106, wherein: the plurality of light emitters 104 emits light in consecutive order to be detected by the at least one sensor 106. The device for monitoring blood 100 has been described as a heart rate monitor.

(94) Furthermore, the embodiments described includes a device suitable for monitoring blood in a body part 100 comprising at least one light emitter 104, a plurality of sensors 106, the at least one light emitter 104 arranged such that light from the at least one light emitter 104 is capable of passing through the body part to arrive at the plurality of sensors 106.

(95) Furthermore, the embodiments described includes a method of obtaining observations of light transmission to monitor heart rate comprising the steps of: providing at least two sensors 106 for detecting light, placing the two sensors 106 at different sides of a body part, providing a first light emitter 104 at another side of the body part, such that light emitted from emitter 104 transmits through the body part to arrive at the at least two sensors 106, the transmission path to one of the sensors 106 providing a first observation, and the transmission path to the other of the sensors 106 providing a second observation.

(96) Furthermore, the embodiments described includes a method of obtaining observations of light transmission to monitor heart rate comprising the steps of: providing at least two light emitters 104, providing a sensor 106 for detecting light, placing the at least two emitters 104 at different positions on a side of the body part, providing the sensor 104 on another side of the body part, such that light emitted from the emitters 104 is capable of transmitting through the body part to arrive at the sensor 106, and operating the emitters 104 one after another to obtain different observations at the sensor 106.

(97) While there has been described in the foregoing description preferred embodiments of the present invention, it will be understood by those skilled in the technology concerned that many variations or modifications in details of design, construction or operation may be made without departing from the scope of the present invention as claimed.

(98) For example, although the sensors 106 have been described to detect light from the emitters 104 transmitted through the body part, it is possible that the sensors 106 can be arranged in other embodiment to detect light from the emitters 104 by reflection or dispersion from the body part. In this case, the sensors 106 would be placed next to but a distance away from the emitters 104.

(99) FIG. 14 shows a further embodiment which is much simpler, comprising only one emitter 104 and two sensors 106 placed across the emitter. Only two observations can be made from the two sensors. This embodiment can be used in situations where noise from movements is very unlikely, such for monitoring the heart rate of an infant, but use of only two sensors and one emitter instead of two sensors and two emitters allow a much lighter, smaller and cheaper device 100.

(100) FIG. 15 and FIG. 16 illustrate yet another embodiment showing how the emitters 104 can be placed adjacent each other on one side of the ring 102 and the sensors 106 placed adjacent each other but on the other side of the ring 102, instead of the configuration in the first embodiment. FIG. 15 shows emitter L2 lighting up first to transmit towards sensor S1 and sensor 2, and FIG. 16 shows emitter L1 lighting up subsequently to transmit towards sensor S1 and sensor S2.

(101) In other embodiments, as shown in FIG. 17, a single emitter 104 is used to project infrared light to be detected by three or more sensors 106. This allows three observations to be made with only one emitter 104 and three sensors 106, instead of thee emitter and three sensors as in the prior art.

(102) FIG. 18 shows how three sensors 106 are used to provide six observations with only two emitters 104. When the emitters 104 emit in consecutive order, the sensors 106 are able to detect six observations. This also provides the advantage that if one of the sensors 106 fail to work, the device 100 as a whole is still functional with two sensors 106 and two emitters 104 providing four observations, which is superior to the use of three observations typical in prior art. In the prior art, each sensor is dedicated to only one emitter and there is therefore no redundancy of observations; the number of observations is the same as the number of sensors 106. Alternatively, in a variation of this embodiment, three emitters 104 and two sensors 106 may be used. In general, use of less emitters 104 with more sensors 106 leads to faster operation than more emitters 104 with less sensors 106, as there is less need of time to wait for each emitter 104 to take its turn.

(103) Although the device 100 has been described as a ring 102, the device may be provided in other forms such as an ear plug 102a, as shown in FIG. 19. The ear plug typically has emitters 104 arranged on the surface of the ear plug to emit light into the ear of the wearer. The tissues surrounding the ear plug reflects the light back to the ear plug. The ear plug also has sensors 106 arranged on the ear plug surface to detect the reflected light. A drawing of an ear plug is shown in FIG. 19 without illustrating the positions of the emitters and sensors. By the term ear plug, the skilled reader should note that it includes any sufficiently stable attachment to the ear that monitors blood, including ear plug which are insertable into the ear hole, or any attachment which can sit just outside the ear hole in the outer ear such as ear phones or any device that can clip to the ear in any way to read light transmission or dispersion in any part of the ear.

(104) Alternatively, the device 100 can be in the form of an arm band 102b instead of a ring 102, as shown in FIG. 20, in which emitters and sensors are installed for projecting and detecting infrared or other light into the arm of the wear for monitoring heartbeat.

(105) Although infrared light has been described in the embodiments, other wavelengths are possible, as it has been found that blood is capable of absorbing other wavelengths including red, green and blue light.

(106) The embodiments can be implemented in oximeters for detecting oxygen level in blood, which operates by contrasting the ratio of transmission of visible red light to transmission of infrared light. The ratio of the amount of absorbed red light to the amount of absorbed infrared light indicates the amount of oxygen in the blood. Therefore, in embodiments having oximeters functions, there may be an emitter emitting red light to the sensor, and an emitter emitting infrared light to the same sensor which is capable of detecting in both ranges of wavelengths. In this case, the red light emitter and the infrared light emitter take turns to emit light. Alternatively, the emitter is capable of emitting red light and infrared light at the same time, but a separate red light sensor and a separate infrared light sensor detects the different wavelengths selectively and at the same time. Alternatively, the oximeters comprises a set of emitters and sensors as described for emitting and sensing only in red light, and comprises a separate set of emitters and sensors as described for emitting and sensing only in infrared only.

(107) Although a digital signal processing method has been described for treating the infrared signals mathematically, other processing methods or other mathematical treatment is possible. Also an analogue treatment for removing the noise instead of the digital ways described is also possible.

(108) It should be noted that the meaning of a ‘pair’ of emitter and sensor is merely functionally defined, and each pair of emitter and sensor may be placed immediately next to each other, such as emitter L1 and sensor S3, or emitter L3 and sensor S2 or emitter L2 and sensor S1 of FIG. 10. Alternatively, in other configurations, any pair of emitter and sensor may be placed apart from each other such as the configuration in the embodiment of FIGS. 1, 2 and 3.

(109) FIG. 21 shows yet another embodiment, which comprises a piece of planar substrate 2101 embedded with two sensors 106 and two emitters 104. The substrate has a generally planar surface for application onto the wearer's body part, i.e. the embodiment may be placed onto a human part with a generally planar surface. Preferably, the substrate comprises a piece of flexible woolen or cotton fabric, or a piece of flexible plastic sheet such as polyvinylchloride. However, any other designs which provides a planar application surface is within the intention of this invention.

(110) The two light emitters 104 and two sensors 106 are embedded into the substrate in such a way that when the substrate is applied onto the wearer's body part, the emitters 104 and the sensors 106 are pressed snugly against the wearer's skin. A suitable housing 108 is also embedded into the substrate which contains the microprocessor and memory required for operating the emitters and sensors, and for recording data as detected by the sensors. The microprocessor, memory, light emitters and sensors, as well as the wiring between them, are not illustrated but the skilled reader will understand that all manner of suitable wiring or printed circuitry may be used to connect microprocessor, memory, light emitter and two sensors one to another to provide the required functions to the embodiment 100.

(111) Preferably, the surface of the substrate to he applied onto a body part of the user is provided with adhesive for securing to the skin of the person, such as those used to stick medical plaster to body parts. FIG. 22 shows how the generally planar substrate 2101 can he plastered or adhered to the arm. The generally planar substrate 2101 can also be adhered to body parts such as the chest or back, or wherever body part is large enough to be adhered with the substrate 2101 without requiring the substrate 2101 to fold significantly or be creased.

(112) Preferably, the adhesive is of a type which is re-useable, such that the substrate 2101 may he peeled off the wearer's body part and be re-applied. onto another body part of the same wearer or another wearer. There are many suitable adhesives that may he re-applied onto a target surface repeatedly. Alternatively, a vacuum application may be used, such as a planar substrate which has small suction cups for sucking onto the wearer's body part. All these technology are known in the art and requires no elaboration here. It is also possible that the planar substrate may he provided with a belt which is tied around the arm, instead of using adhesive or suction cups. The belt in this case is merely an accessory and does not contribute to the arrangement, or the possibility of different arrangements, of the sensors and emitters.

(113) FIG. 23 and FIG. 24 show one possible way in which the sensors 106 and the emitters 104 may be embedded into a substrate 2101. The substrate 2101 is shown in the sidewise cross-section, and comprises a backing layer 2301 and an application layer 2303 which are pressed together. For ease of illustration, two emitters and one sensor is shown in FIG. 23 and FIG. 34, while the other sensor is not shown. It suffices that in FIG. 21, the emitters and sensors are shown to be arranged in such a way that no subset of any two emitters and one sensor, or subset of any two emitters and one sensor, forms a straight line, which prevents the two sensors from detecting the same noise caused by the same wearer movements.

(114) The application layer 2303 has suitable holes cut out to allow the operational parts of the emitters and sensors to peek out of the substrate 2101, which is to say, the emitters are able to emit light from the substrate 2101 onto the wearer, and the sensors are able to detect light from the surroundings through the holes. The backing layer 2301 and the application layer 2303 generally enclose the emitters and sensors like a sandwich. The housing 108 containing the microprocessor and memory, however, may be completely encased within the backing layer and the application layer without need of being accessible to the wearer, which serves to protect the housing from damage.

(115) FIG. 24 shows how the emitters 104 and sensors 106 are operated to detect heart rate of the wearer on whose skin is the substrate 2101 applied. The emitters emit light into the skin of the wearer. The light penetrates into the wearer's skin and tissue to be diffused and scattered 2401. Some of the scattered light is reflected towards the sensors 106. However, a portion of the light is absorbed by blood. Blood content in the skin is not constant but changes with the beating of the heart. Therefore, light scattered back towards the sensors has a pulsating intensity. By monitoring this pulsating intensity, the sensors are able to monitor pulsating blood flow and hence monitor heart rate of the wearer.

(116) To ensure that the heart rate signals detected by each sensor have different noise components despite being caused by the same wearer movements, the two emitters are placed as far apart from each other as possible and preferable at a respectively different angle to each sensor within the plane of the substrate 2101. That is, the emitters do not form a straight line with each sensor, and each emitter emits light to the same sensor in a different direction to that of the other emitter. in this way, the influence of motion on light transmitted from each of the emitters reaching the same sensor is different, and may possibly be cancelled out by summing the sensor readings of the light transmission from two emitters.

(117) By comparison, if the emitters form a straight line with a sensor, movement vectors of the wearer along the line might be undetected, or even accentuated if the transmissions of two emitters are added together.

(118) In order that the sensor is able to detect light more sensitively from both emitters 104, the microprocessor operates the emitters 104 such that they emit infrared light sequentially. Thus, the sensor S1 first detects infrared light scattered through skin and tissue from the one emitter L1 (FIG. 25) via path P11. At the same time, the sensor S2 detects infrared light scattered through skin and tissue from one emitter L1 (FIG. 25) via path P12. The infrared signals observed by the sensor S1 and by the sensor S2 are recorded for processing by the microprocessor. Subsequently, the microprocessor instructs emitter L1 to stop emitting infrared light and instructs emitter L2 to start emitting infrared light. The sensor S1 then detects the infrared signals via transmission path P21 and sensor S2 detects the infrared signals via transmission path P22. in this way, the embodiment in FIG. 21 to FIG. 26 provides a planar or generally planar device which can accurately determine heart rate of the wearer, with noise components which is caused by wearer movements easily cancelled out in four observations of transmissions i.e. P11, P12, P21 and P22, using only two emitters and two sensors.

(119) In a variation of this embodiment, the substrate 2101 is a non-flexible, stiff, substrate 2101 having a generally planar but curved surface conforming to the contours of the arm or other body part intended for wearing the embodiment. Such slight curvature is within the meaning of ‘planar’ here, and does not encircle around the entire body part, i.e. different from an arm band or ring. For example, the top of a helmet may be installed with the proposed substrate 2101, which can sit on the head of the wearer to monitor heart rate. The hard substrate 2101 can be made of hard plastic, clay or stiffened leather and so on.

(120) FIG. 27 shows a planar device having three emitters and one centrally placed sensor, in which the emitters take turns to transmit light through the skin and tissue of the wearer to the sensor, each from a different direction. Preferably, the emitters are arranged space apart from each other by 120 degrees. However, this is not necessary as long as the emitters do not experience the same motion artefacts, which is provided by pointing towards the sensor from different directions. Being in different positions, the transmissions do not acquire the same noise despite being caused by the same wearer movements. Hence the common signal read from the three emitters is the heart rate of the wearer which may be amplified by summing the signals together. FIG. 28 shows a reverse configuration of the embodiment of FIG. 27 in which a single emitter transmit light to three sensors sequentially, each sensor arranged in a different direction to the single emitter. In this case, the light transmission may be continuous and the sensors operate sequentially, one after another. Alternatively, however, the sensors are also in operation continuously.

(121) FIG. 29, FIG. 30, FIG. 31, FIG. 32 and FIG. 33 illustrate another planar embodiment. FIG. 29 is the plane view of the embodiment showing two emitters L1, L2 arranged with two sensors, S1, S2 embedded into a planar substrate 2101, such that each emitter is able to project to the two sensors. The two sensors are each placed in a different angle to each of the emitters, which ensures that the transmission from each emitter reaches either sensor in a different angle.

(122) The light emitter is preferably an LED which is selected to project a narrow beam. The beam is illustrated in FIG. 30. The origin of the beam is the LED and is represented by the letter o. The centre arrow represents the direction to which the LED is pointed and is the main incident ray. The LED is also selected such that the narrow beam projects an elongate, oval beam spot. The spot is longer and more powerful along line rq, and narrower and weaker along line sp. The cause of this oval beam spot is due to the typical housing of an LED, giving a non-circular beam spot as a natural product imperfection. Therefore, there is no need for an LED to be specifically manufactured to provide an oval beam spot, under normal circumstances.

(123) The light rays along rq penetrate relatively deeper into the tissue of the wearer of the embodiment. The light rays along sp penetrate to a relatively lesser extent into the tissue of the wearer of the embodiment. This is illustrated schematically in FIG. 32 and FIG. 33.

(124) Strictly, scattering of light happens at every layer of skin and tissue. However, the intensity of light being scattered is different at different layers of the skin ad tissue. The reason for ‘deeper penetration’ of light rays along pq is because stronger intensity allows the ray of light to be scattered at every layer of the skin and tissue while yet having enough intensity to reach the deeper layers before the rebounding light is too weak be detected by sensors at the skin surface. If strong enough to be detected when it reaches the sensors, light rebounded from deeper layers carries information about these deeper layers.

(125) For the weaker light intensity in the sp direction, much of the ray of light would have dissipated before it reaches very deeply into the skin and tissue. Any tiny bit of this ray of light which manages to reach deep into the skin and tissue is unlikely to be rebounded towards the sensors in detectable intensity. Hence, scattered light of this weaker intensity is mostly rebounded at the shallower layers of skin and tissue, and carries more information of these shallower layers than of deeper layers.

(126) FIG. 32 shows the case Where an LED is provided as the ‘first’ emitter L1 (the one on the bottom left of FIG. 29) arranged such that the axis rq of its beam spot is aligned with axis-b. The penetration of the LED's light in this axis is along the length of the oval shape of the beam spot, is relatively deep and passes through some deeper blood vessels 3201 along rq. As explained, light is scattered by tissue and blood at every layer in the tissue but a good portion of intense light is scattered or rebounded only after it has penetrated deeply. Scattering of the light in the deeper tissue is less prone to the influence of motions of the wearer on the embodiment. A ‘first’ sensor S1, i.e. the one shown in the bottom right of FIG. 29, is arranged to sense scattered light which originates along axis-b. Scattered light carrying information on pulsating blood flow received by the ‘first’ sensor S1 is less influenced by movement artefacts because of the deeper light penetration and scattering.

(127) FIG. 33 shows the case where the rays along sp axis of the beam spot from the same ‘first’ emitter L1 are aligned with axis-a, that is, the rays along the breath of the oval shape of the beam spot. The scattered rays along axis-a reaches the second sensor S2 (the one provided on the upper left of FIG. 29). In other words, both the first sensor S1 and second sensor S2 receive light transmissions from the same first emitter L1. However, light penetration is shallower along axis-a. Scattering or rebounding of light therefore takes place largely in the shallower layers of skin and tissue. When light from the LED is scattered nearer to the surface of the wearer's body part, it is more likely that motion artefacts are present as noise in the signal generated by scattering of the light. Therefore, scattered light carrying information on pulsating blood flow received by the ‘second’ sensor S2 along axis-a, which is the sensor shown in the one in the upper left corner in FIG. 29, is more influenced by movement artefacts and has more noise. However, the noise is made up of different noise components from those in the scattered light detected by S1.

(128) Accordingly, the light transmissions detected by both sensors S1 and S2 comprise respectively different noise signals. Their noise signals are distinct one from the other due to both the sensors' different positions to the same emitter L1, and also by the different depths of tissue penetration and scattering of light. The different directions of the sensors to the same emitter L1 ensure that wearer movements in the three-dimension impart different noise signals onto the readings of the sensors S1, S2. The only common, identical signal component in the readings of both sensors S1, S2 is therefore the heart rate signal, caused by the pulsation of blood in the tissue. The greater the difference between the noise signals in the readings of both sensors, the easier it is to cancel out the noise and to amplify the heart rate signal by merely adding the signals of the two sensors S1, S2.

(129) Once the sensors S1 and S2 have read the light transmission from the first emitter L1, the first emitter L1 is switched off and the second emitter L2 is switched on. The frequency of switching over between emitter L1 and emitter L2 may be in periods of milli-seconds to a few seconds, as long as heart rate may be represented or reconstructed from the signals detected by the sensors S1 and S2 (that is, a single heartbeat may be read in discrete portions by the sensors alternating in periods of milli-seconds and concatenated to produce the complete heartbeat signal, as illustrated in FIG. 34. Preferably, the period between switching over from S1 to S2, or vice versa, is 2 milli-seconds to 200 milli-seconds). The converse then happens: an LED provided as the ‘second’ emitter L2 (the one on the top right of FIG. 29 is arranged such the respective axis rq of this second emitter L2 is aligned with axis-b. The penetration of the light of the second emitter L2 in this axis is along the length of the oval shape of the beam spot, is relatively deep and passes through some deeper blood vessels. The ‘second’ sensor S2 is able to sense scattered light which originates along axis-b from L2. Again, scattered light carrying information on pulsating blood flow received by the ‘second’ sensor S2 is less influenced by movement artefacts because of the deeper light penetration and scattering. Furthermore, the rays along the respective axis sp from the same ‘second’ emitter L2 are aligned with axis-a, that is, the rays along the breath of the oval shape of the beam spot. The scattered rays along axis-a reach the first sensor S1. In other words, subsequent to receiving light emitted from emitter L1, both the first sensor S1 and second sensor S2 then receive light transmissions from the second emitter L2. Light penetration is shallower along axis-a. Therefore, scattered light carrying information on pulsating blood flow received by the first sensor S1 along axis-a from L2 is more influenced by movement artefacts and has more noise. The only common, identical signal component in the readings of both sensors S1, S2 is the heart rate signal, caused by the pulsation of blood in the tissue. The noise is eliminated and the heart rate is amplified by merely adding the signals of the two sensors S1, S2.

(130) Therefore, when the first emitter L1 is switched on, S2 reads a signal along the path P12, and S1 reads a signal along the path P11. The signal, in this embodiment, along P11 penetrates deeper than the signal P12. Both S1 and S2 read their signals from L1 at the same time. When the second emitter L2 is switched on, S2 reads a signal along the path P22, and S1 reads a signal along the path P21. The signal, in this embodiment, along P22 penetrates deeper than the signal P21. Both S1 and S2 read their signals from L2 at the same time. Accordingly, the four observations obtained from the two sensors S1, S2 can be modelled as equations (1), (2), (3) and (4) as discussed above. The noise components in these four observations are even more distinct from that in each other because of the different depth penetration of the LED light emitted in different directions.

(131) In a variation of the embodiment, each of the sensors S1 and S2 takes turns to read from the first emitter L1, and then each of the sensors S1 and S2 takes turns to read from the second emitter L2. This makes the four observations of the sensors even more independent from each other.

(132) In general, the embodiment provides a different transmission route between each permutation of emitter and sensor pair, such that the same movement of the wearer will end up causing as varied a noise in the readings of each emitter and sensor pair as possible. The variation can be provided by different direction between each emitter and sensor pair, or by different depth of skin and tissue penetration between each emitter and sensor pair or both. The greater the variation and randomness between the noise in the readings of each emitter and sensor pair, the more likely those noise can be eliminated to retrieve the wearer's heart rate signal which is the common component in the signal of each emitter and sensor pair.