Source: https://insight.rpxcorp.com/pat/US20080200785A1
Timestamp: 2019-12-14 23:44:15
Document Index: 86210720

Matched Legal Cases: ['art.\n6', 'art.\n9', 'art;\n19', 'art.\n22', 'art 3', 'art 3']

Patent US 20080200785A1
1. . A signal processing device comprising:
(d) a filter receiving the reference signal as an input, wherein the filter essentially separates a supplementing signal and a favored signal from the signals generated by the detector,wherein the favored signal is a measure of the physiological characteristics.
2. . The signal processing device according to claim 1, wherein each of the measurement radiation of (a) is of different wavelength.
3. . The signal processing device according to claim 1, wherein the measurement radiation of (a) propagates wholly or partially along a propagation path situated in the propagation medium
4. . The signal processing device according to claim 1, wherein the pressure of (b) is a time-variable pressure.
5. . The signal processing device according to claim 1, wherein the propagation medium is a human body part.
6. . A device for measuring one or more physiological characteristics, the device comprising(a) at least one radiation source for generating at least one measurement radiation, wherein the measurement radiation propagates through a body part;
(e) a filter receiving the reference signal, wherein the filter essentially separates a supplementing signal and a favored signal from the signals measured by the detector,wherein the favored signal is a measure of the physiological characteristics.
7. . The device according to claim 6, wherein each of the measurement radiation of (a) is of different wavelength.
8. . The device according to claim 6, wherein the measurement radiation of (a) propagates wholly or partially along a propagation path situated in the body part.
9. . The device according to claim 6, wherein the pressure of (c) is a time-variable pressure.
10. . The device according to claim 6, wherein the physiological characteristics comprise blood characteristics.
11. . The device according to claim 6, wherein the physiological characteristics comprise arterial and venous characteristics.
12. . The device according to claim 6, wherein the physiological characteristics comprise blood pressure characteristics.
13. . The device according to claim 6, wherein the physiological characteristics comprise arterial oxygen saturation.
14. . The device according to claim 6, wherein the physiological characteristics comprise venous oxygen saturation.
15. . The device according to claim 6, wherein each of the at least one measurement radiation of (a) is of defined, mutually differing wavelengths.
16. . A signal processing device comprising:
(c) a reference signal generator, which accepts the signals s1(t) to sN(t) measured by the detector and the pressure signal p(t) as inputs and computes from these inputs a reference signal Δ
(t), which is a function of the second, time-variable quantity v(t) or of the supplementing signals v1(t) to vN(t); and
(d) a filter receiving the reference signal Δ
(t) as an input, wherein the frequency properties of the filter essentially correlate with the reference signal Δ
(t), and wherein the filter essentially separates from at least one of the signals s1(t) to sN(t) measured by the detector the supplementing signal v1(t) to vN(t) from the favored signal a1(t) to aN(t).
17. . A device for the continuous, non-invasive measurement of the arterial blood flow comprising:
(d) a reference signal generator, which has as inputs the signals s1(t) to sN(t) measured by the detector and the pressure signal p(t), and which computes from these inputs a reference signal Δ
(t), which is a function of the venous blood flow v(t) or of the venous signal components v1(t) to vN(t); and
(e) a filter receiving the reference signal Δ
(t) as an input, where the frequency properties of the filter essentially correlate with the reference signal Δ
(t), and wherein the filter essentially separates from at least in one of the signals s1(t) to sN(t) measured by the detector the venous signal component v1(t) to vN(t) from the arterial signal component a1(t) to aN(t), wherein the arterial signal component is proportional to the arterial blood flow a(t).
18. . A pulse oximeter comprising(a) at least one radiation source for generating at least one measurement radiation, wherein the measurement radiation propagates through a body part;
19. . A method for measuring one or more physiological characteristics, the device comprises(a) providing a first and at least one other measurement radiation;
(e) separating a supplementing signal component and a favored signal component from the measurement signals of (b) by using a filter that receives a reference signal as an input, wherein the reference signal is computed from the measurement signal of (b) and the pressure signal of (c),wherein the favored signal component is a measure of the physiological characteristics.
20. . The method according to claim 19, wherein each of the measurement radiation of (a) is of different wavelength.
21. . The method according to claim 19, wherein the measurement radiation of (a) propagates wholly or partially along a propagation path situated in the body part.
22. . The method according to claim 19, wherein the pressure of (c) is a time-variable pressure.
23. . The method according to claim 19, wherein the physiological characteristics comprise blood characteristics.
24. . The method according to claim 19, wherein the physiological characteristics comprise blood characteristics.
25. . The method according to claim 19, wherein the physiological characteristics comprise arterial and venous characteristics.
26. . The method according to claim 19, wherein the physiological characteristics comprise blood pressure characteristics.
27. . The method according to claim 19, wherein the physiological characteristics comprise arterial oxygen saturation.
28. . The method according to claim 19, wherein the physiological characteristics comprise venous oxygen saturation.
29. . The method according to claim 19, wherein each of the at least one measurement radiation of (a) is of defined, mutually differing wavelengths.
30. . A method for the continuous, non-invasive measurement of arterial blood pressure in a body part with arterial and venous blood flow comprising:
(d) computing a reference signal Δ
(t) from the signals s1(t) to sN(t) and the pressure signal p(t), which is a function of venous blood flow v(t) or of the supplementing signal components v1(t) to vN(t); and
(e) separating the supplementing signal component v1(t) to vN(t) from the favored signal component a1(t) to aN(t) of the signals s1(t) to sN(t) measured by a detector by means of a filter receiving the reference signal Δ
(t) as an input, wherein the frequency properties of the filter essentially correlates with the reference signal Δ
(t), and wherein the favored signal component a1(t) to aN(t) is proportional to the arterial blood flow a(t).
31. . The method according to claim 30, wherein the frequency properties of the filter are adaptively modified during signal analysis by means of the reference signal.
32. . The method according to claim 30 or 31, wherein from the frequency properties obtained by measuring the blood pressure, the arterial oxygen saturation aSpO2 and/or the venous oxygen saturation vSpO2, are derived and displayed.
33. . The method according to any of claims 30 or 31, wherein red light is used as the first measurement radiation and infrared light is used as the second measurement radiation.
34. . The method according to claim 32, wherein red light is used as the first measurement radiation and infrared light is used as the second measurement radiation.
35. . The method according to claim 33, wherein the red light is of wavelength 660 nm and the infrared light is of wavelength 940 nm.
36. . The method according to claim 34, wherein the red light is of wavelength 660 nm and the infrared light is of wavelength 940 nm.
FIGS. 5a to 5c show variants of the output-power diagrams of the filters.
FIGS. 6a to 6c show further variants of the output-power diagrams of the filters.
FIGS. 5a to 5c show diverse possibilities for output power diagrams. FIG. 5a shows typical output power of the J filters, for arterial oxygen saturation aSpO2=96% (ra=0.612) and venous oxygen saturation vSpO2=72% (rv=1.476). At r=1 (SpO2=86.7%) a local peak of output power occurs due to the feedback of pressure on the body part 3, which acts on the signals sR(t) and sIR(t) obtained by LEDs 1 and 2. The decision matrix 18 can distinguish precisely between aSpO2 (ra) and vSpO2 (rv).
FIG. 5b shows filter behaviour when venous blood flow is small or only influenced by the pressure p(t), which is the case at r=1. There is very little variable venous blood flow caused for instance by movement of the body part 3. But arterial blood flow at the site aSpO2=96% (ra=0.612) and the feed-back peak can be clearly seen. The decision matrix 18 recognizes that no corrupting influence due to venous blood flow is present and is able to compute a(t) directly from one of the two unfiltered signals sR(t) and sIR(t). Only aSpO2 can be displayed, however, which is usually sufficient for the user.
FIG. 5c shows the same kind of behaviour—here too the influence of venous blood flow on output power is small. In this instance oxygen saturation aSpO2=87% (ra=0.989) and thus the output power for ra is superimposed on that for r=1. For the decision matrix 18 this signifies that aSpO2=87% is displayed and that no corrupting influence due to venous blood flow is present (same as in FIG. 5b).
s(t)=Δs(t)+s0
p(t)=SP+h(s(t)−smean)=SP+h(Δs(t)+s0−smean)=SP+h(Δs(t)),
s(t)=Δs(t)+s0−g(p(t))
p(t)=g−1(Δs(t)+s0)=SP+h(Δs(t)) or
p(t)−p0=g−1(Δs(t))=h(Δs(t))
s(t)=a(t)+v(t)+s0
sR(t)=aR(t)+vR(t)+sR0 red light measured signal
sIR(t)=aIR(t)+vIR(t)+sIR0 infrared light measured signal
aR(t)=ra*aIR(t)=ra*a(t)
vR(t)=rv*vIR(t)=rv*v(t)
sIR(t)=a(t)+v(t)+sR0
sR(t)=ra*a(t)+rv*v(t)+sIR0
ΔsR(t)=ra*a(t)+rv*v(t)
ΔsR(t)=ra*(ΔsIR(t)−v(t))+rv*v(t)
ΔsR(t)−ra*ΔsIR(t)=rv*v(t)−ra*V(t)
sIR(t)=a(t)+v(t)+sIR0−g(p(t))
sR(t)=ra*a(t)+rv*v(t)+sR0−g(p(t))
sIR(t)=a(t)+v(t)+sIR0−g(SP+h(a(t)))
sR(t)=ra*a(t)+rv*v(t)+sR0−g(SP+h(a(t)))
n(t)=sR(t)−ra*sIR(t)
n(t)=ra*a(t)+rv*v(t)+sR0−g(SP+h(a(t)))−ra*(a(t)+v(t)+sIR0−g(SP+h(a(t))))
Δn(t)=rv*v(t)+sR0−g(SP+h(a(t)))−ra*v(t)−ra*sIR0+ra*g(SP+h(a(t)))
Δn(t)=v(t)*(rv−ra)+g(SP+h(a(t)))*(ra−1)
Δn(t)=v(t)*(rv−ra)+g(SP+p(t))*(ra−1)
Δn′(t)=v(t)*(rv−ra)+g(SP+Δp(t))*(ra−1)−h−1*(SP+Δp(t))*(ra−1)
Δn′(t)=v(t)*(rv−ra)
n(t)=sR(t)−r*sIR(t)
n(t)=ra*a(t)+rv*v(t)+sR0−g(SP+Δp(t))−r*(a(t)+v(t)+sIR0−g(SP+Δp(t)))
Δn(t)=(ra−r)*a(t)+(rv−r)*v(t)+(r−1)*g(SP+Δp(t))
Δn′(t)=(ra−r)*a(t)+(rv−r)*v(t)+(r−1)*g(SP+p(t))−(r−1)*h−1(SP+p(t))
Δn′(t)=(ra−r)*a(t)+(rv−r)*v(t)
Δn′(t)=(ra−r)*a(t)+(rv−r)*v(t)+c*(r−1)*g(SP+Δp(t))
Δn′(t)=sR(t)−r*sIR(t)−mean(sR(t)−r*sIR(t))−(r−1)*h−1(SP+Δp(t))
Δn′(t)=ΔsR(t)−r*ΔsIR(t)−(r−1)*h−1(p(t))
r=ra Δn′(t)=(rv−ra)*v(t)+c*(ra−1)*g(p(t)) 1)
r=rv Δn′(t)=(ra−rv)*a(t)+c*(rv−1)*g(p(t)) 2)
r=1 Δn′(t)=(ra−1)*a(t)+(rv−1)*v(t) 3)
r≠ra,r≠rv,r≠1 Δn′(t)=(ra−r)*a(t)+(rv−r)*v(t)+c*(r−1)*g(p(t)) 4)