Novel optical interferometric scanning detector for cardiovascular function monitoring

Abstract

The object of the present invention is to disclose a novel optical miniaturized handheld medical device for convenient monitoring and/or data collection of detailed signals on human cardiovascular function. The implementation consists of a number of advanced technologies, including interferometric detection, phase controlled focusing beam steering, auto-tracking scheme and algorism, and integrated optical chip assembly to enhance the device's performance and miniaturization. Briefly, this handheld medical device directs a single or dual output laser beam(s) onto certain skin surface to detect the surface vibration velocity at the point where the laser hits the surface. The skin surface vibrates in response to cardiovascular signals, such as blood pressure pulses, turbulent blood flow through narrowed arteries, pumping actions of the heart, or the closure of the heart valves etc. The miniaturized apparatus thus is capable of detecting these signals for the assessment of cardiovascular functions in both healthy and disease conditions.

Claims

1. An apparatus or method for detecting movement (vibration signal) on human skin surface for cardiovascular function monitoring, comprising: an integrated optical interferometric scanning system with self-tracking function; a control and data processing unit; and a communication unit.

2. The apparatus or method of claim 1, wherein said integrated optical interferometric scanning system with self-tracking function comprises: A laser beam toward said skin surface of said subject and a reflected laser beam detected by a laser interferometer configured to detect said reflected laser beam and through said detection, determining one or more variables related to the vibration of said targeted skin surface; and A laser beam guiding and tracking scheme based on angle or position steering to locate said blood vessel steers said laser beam to said sensing area and locks said laser beam to said targeted location under all circumstances.

3. The apparatus or method of claim 1, wherein said control and data processing unit is configured for general system control and preliminary data processing of said vibration signals of said skin surface.

4. The apparatus or method of claim 1, wherein said communication unit is configured for transferring and displaying said vibration signals of said skin surface to nearby paired smart devices (phones, tablets etc.) or clouds, through wireless technology, such as BLE, Wi-Fi, or LTE.

5. An apparatus or method for monitoring the cardiovascular function by analyzing the cardiovascular signals extracted from said vibration signals collected through a miniaturized handheld device that is based on integrated optical interferometric scanning technology.

6. The apparatus or method of claim 5, wherein said cardiovascular signal is arterial blood pressure-related pulse wave.

7. The apparatus or method of claim 5, wherein said cardiovascular signal is turbulent sound produced by blood flow through a narrowed artery.

8. The apparatus or method of claim 5, wherein said cardiovascular signal is the rhythm and/or synchronicity of the heart beats (contractions).

9. The apparatus or method of claim 5, wherein said cardiovascular signal is heart sound(s) produced by the closure of the heart valve(s) or the filling of the heart.

10. The apparatus or method of claims 5-9, wherein the biometric of said cardiovascular signal is the velocity of said skin surface vibration as a function of time.

11. The apparatus or method of claim 6, wherein said cardiovascular signal is pulse wave, PWV, and further comprising the step of producing blood pressure measurement including determination of pulse rate, systolic and diastolic blood pressure, dicrotic notch, and duration of systole and diastole by plotting skin surface displacement as a function of time.

12. The apparatus or method of claim 8, wherein said cardiovascular signal is heart beat and further comprising the step of determination of heart rate, synchronicity of the left and right atria, the left and right ventricles, and the walls of ventricles by plotting skin surface displacement as a function of time.

13. The apparatus or method of claim 9, wherein said cardiovascular signal is heart sound(s), wherein the first sound produced by the closure of the mitral and tricuspid valves, the second by the closure of the aortic and pulmonic valves, the third by the early, passive diastolic filling of the ventricles, and the fourth by the late, active filling of the ventricles due to atrial contraction, and other extra-heart sounds that cause the movement/vibration of the chest wall by plotting skin surface displacement as a function of time during cardiac cycles.

14. The apparatus or method of claims 5-13 further comprise general system control and preliminary data processing of said cardiovascular signals, wherein the biometric of the cardiovascular signal is the velocity of the skin surface vibration as a function of time.

15. The apparatus or method of claims 5-13 further comprise transferring and displaying said cardiovascular signals on a remote device, wherein the biometric of the cardiovascular signal is the velocity of the skin surface vibration as a function of time.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0019] The present invention is illustrated and described herein with reference to the various drawings of exemplary embodiments, in which like reference numbers are used to denote like system components/method steps, as appropriate.

[0020] FIG. 1 is a schematic diagram of the design for the integrated optical scanning sensor chipset with multiple functions, such as Interferometric focusing beam steering, I/Q balanced detection, etc., for the purpose of detection and monitoring of the cardiovascular signals.

[0021] FIG. 2 is a schematic diagram of an exemplary implementation of the miniaturized device comprising of three major parts for convenient cardiovascular signals monitoring.

[0022] FIG. 3 is a conceptual drawing illustrating the possible mechanical design of the miniaturized device with two optical scanning sensors implemented.

[0023] FIG. 4 is a schematic diagram of the scanning zone and location of the optical scanning beam on the targeted scanning skin surface.

[0024] FIG. 5 is a schematic diagram of the potential areas of human body to which the miniaturized device can be applied and exemplary signals at the chest wall (for heart) or at certain skin surfaces (for blood vessels).

DETAILED DESCRIPTION OF THE INVENTION

[0025] Consistent with the inventions of Interferometric focusing beam optical cardiovascular sensor, U.S. patent application Ser. No. 15/146,354 and 1D laser beam guiding and tracking system and method for interferometric focusing beam optical cardiovascular sensor, U.S. patent application Ser. No. 15/235,656, this invention describes the implementation of a miniaturized handheld medical device for the cardiovascular signals monitoring purpose.

[0026] Referring to FIG. 1, this is an integrated optical waveguide chipset 100 that consists of 6 major functional parts: the laser source 20, the tap coupler 30, the light emitting part 40, the light receiving part 50, the 24 interferometric mixer 60 and the 2-pair balanced detectors 70. On the optical chip, laser source 20 generates the 1.sup.st laser 101. The tap coupler 30 receives the 1.sup.st laser and splits it into the 2.sup.nd laser 102 and the reference light 104. The 2.sup.nd laser 102 is received by the light emitting part 40 and converted into the 3.sup.rd laser 80, where the 3.sup.rd laser can shine on the targeted scanning skin surface 140 at controllable output angle or output position. Its phase is constant but the amplitude can be dithered as a function of time t for laser beam guiding and tracking purpose. The diffused reflection light from the targeted scanning surface 140, the 4.sup.th laser light 90, has an angle dependent distribution. At the targeted scanning skin surface 140, the phase of 4.sup.th laser light 90 is modulated by local cardiovascular event(s). Only a portion of the 4.sup.th laser light 90 with optimized reflection angle or position can be received or collected by light receiving part 50. The light receiving part 50 converts the 4.sup.th laser light 90 into the 5.sup.th laser light 103. The 5.sup.th laser light 103 is mixed with the reference light 104 inside the 24 interferometric mixer 60, generating the 6.sup.th laser light 105, which contains a set of optical beating signals +I/I 105-1, 105-2, +Q/Q 105-3, 105-4. In balanced detectors 70, the 6.sup.th laser light 105 is converted into electrical signals.

[0027] As an option, the visible red-color light source 120 generates the 1.sup.st red-color light 106. The slab waveguide 107 receives the 1.sup.st red-color light 106 and shines it onto the targeted scanning skin surface 140, forming a visible 1D linear marker on the targeted skin surface 140.

[0028] The system diagram of the proposed miniaturized medical device for cardiovascular signals monitoring can be found in FIG. 2. The miniaturized device 200 consists of three major parts: 1) Two optical scanning sensor chipsets 100-1 and 100-2, each to detect a linear targeted skin surface with distance about 1.5-2 cm. In combination, they work together to collect timing sensitive waveforms for key parameters calculation, such as local pulse wave velocity (PWV). Normally, these two optical scanning sensors are integrated into one chipset; 2) The control and data processing unit 150, performs the general control of optical interferometric scanning sensor chipset as well as the steering/switching and tracking algorithm for both emitting and receiving laser beams. It also does preliminary data processing before sending the data out to either nearby paired smart devices (phones, tablets etc.) or the clouds; 3) The communication unit 160 is responsible for the communication between the miniaturized medical device and nearby paired smart devices (phone, tablet etc.) or remote clouds through BLE, Wi-Fi or LTE.

[0029] Referring to FIG. 3, the conceptual design of the miniaturized medical device 200 could be a palm size rectangular prism. At the bottom end, there are two open slots 230 serving as open windows for two scanning laser beams, which are bout 1.5-2 cm apart. It may also have two supporting structures 220-1 and 220-2 with suitable materials as the buffer between the miniaturized medical device 200 and the target scanning skin surface 140. On the front side, it may have one LCD display and few buttons 210 for device control and communication purpose.

[0030] Referring to FIG. 4, with two built-in optical scanning sensors 100-1 and 100-2, the miniaturized device 200 can perform laser beam steering and scanning along the two separate lines, marked by visible red-color lights 135-1 and 135-2. As the emitting laser beam 80 of each optical scanning chipset can be steered or switched to N directions in 1D, the device can scan multiple spots 136-1-1, 136-1-2, . . . 136-1-N, and 136-2-1, 136-2-2, . . . 136-2-N, simultaneously, on the targeted scanning skin surface.

[0031] Referring to FIG. 5, it illustrates that this miniaturized device 200 can be attached to multiple areas of human body for different detecting purposes, such as 1) the neck (for carotid artery); 2) forearm (for brachial artery) or wrist (for radial artery); 3) leg (for femoral artery) or ankle (for dorsalis pedis artery); or 4) the chest or thorax (for the heart). At the chest, the apparatus could detect the skin movement 310 due to the pumping action of the heart or 320 to the closing of the heart valves (heart sounds). Whereas at the neck or the extremities, the apparatus detects the skin movement 330 due to pressure-related artery displacement resulting in pulsating waveforms or 340 to turbulent blood flow through stenosed (narrowed) arteries, wherein the extent and accurate position of the stenosis can be calculated and located.