阅读说明：本技术 一种无线超声监测设备 (Wireless ultrasonic monitoring equipment ) 是由 A.A.布林利拉贾戈帕尔 A.拉贾戈帕尔 于 2019-08-21 设计创作，主要内容包括：本公开的一些实施方式涉及一种超声测量设备,包括:多个超声传感器,用于捕获生理结构的断层成像信息,每个超声传感器包括具有相应谐振频率的换能器,其中每个换能器具有与另一个换能器的频率响应部分地重叠的频率响应；以及处理设备,用于控制和处理由超声传感器进行的测量。该设备可以被并入到粘合基板中,该粘合基板被配置为与患者的动脉对准地粘附到患者的皮肤。处理设备可以使用多个超声传感器通过执行以下操作来计算通过动脉的平均动脉压：使用多个超声传感器来测量动脉的周长；使用相同的超声传感器来测量血液流动速度；以及使用所测量的动脉周长和血液流动速度来计算平均动脉压。(Some embodiments of the present disclosure relate to an ultrasound measurement device comprising a plurality of ultrasound sensors for capturing tomographic information of a physiological structure, each ultrasound sensor comprising a transducer having a respective resonant frequency, wherein each transducer has a frequency response that partially overlaps with a frequency response of another transducer; and a processing device for controlling and processing the measurements made by the ultrasonic sensor. The device may be incorporated into an adhesive substrate configured to adhere to the patient's skin in alignment with the artery. The processing device may calculate mean arterial pressure through the artery using the plurality of ultrasound sensors by performing the following operations: measuring a circumference of the artery using a plurality of ultrasound sensors; measuring blood flow velocity using the same ultrasonic sensor; and calculating mean arterial pressure using the measured arterial circumference and blood flow velocity.)

1. An ultrasonic measurement device comprising:

a plurality of ultrasound sensors configured to capture tomographic information of a physiological structure, each of the plurality of ultrasound sensors comprising a transducer having a respective resonant frequency, wherein each transducer has a frequency response that partially overlaps a frequency response of another transducer; and

a processing device for controlling and processing the measurements made by the plurality of ultrasonic sensors.

2. The ultrasound measurement device of claim 1, wherein during the capturing of tomographic information of the physiological structure, each of the transducers is configured to be actuated in a time-staggered manner to capture images of a surface of the physiological structure at a plurality of depths.

3. The ultrasonic measurement device of claim 1, further comprising: a substrate, wherein the substrate comprises an adhesive surface for adhering to the skin of a patient, wherein the plurality of ultrasound sensors are incorporated into the substrate.

4. The ultrasonic measurement device of claim 3, wherein the substrate comprises one or more alignment marks for aligning the device with an artery of a patient.

5. The ultrasonic measurement device of claim 4, wherein after the substrate is aligned with an artery, the processing device is configured to calculate a mean arterial pressure through the artery using the plurality of ultrasonic sensors.

6. The ultrasound measurement device of claim 5, wherein the processing device is configured to calculate a mean arterial pressure through an artery using the plurality of ultrasound sensors by performing the operations of:

measuring a circumference of an artery using the plurality of ultrasound sensors;

measuring a blood flow velocity using the plurality of ultrasonic sensors; and

the mean arterial pressure is calculated using the measured circumference of the artery and the blood flow velocity.

7. The ultrasonic measurement device of claim 6, wherein:

a circumference of the artery is measured using echo mode ultrasound imaging with the plurality of ultrasound sensors; and

the blood velocity is measured using continuous wave ultrasound with the plurality of ultrasound sensors.

8. The ultrasonic measurement device of claim 5, further comprising: a wireless transmitter, wherein the wireless transmitter is configured to transmit the calculated mean arterial pressure to a display system for display.

9. The ultrasonic measurement device of claim 5, further comprising: a display, wherein the display is configured to display the calculated mean arterial pressure.

10. The ultrasound measurement device of claim 5, wherein the processing device is configured to iteratively recalculate a mean arterial pressure through an artery using the plurality of ultrasound sensors to account for beat-to-beat variations in arterial pressure.

11. The ultrasonic measurement device of claim 2, further comprising: a plurality of non-ultrasonic sensors, wherein each of the plurality of non-ultrasonic sensors is configured to make measurements that are correlated and normalized to ultrasonic measurements made by the plurality of ultrasonic sensors.

12. A method, comprising:

aligning a substrate with an artery of a patient, wherein the aligned substrate comprises an ultrasound measurement device comprising a plurality of ultrasound sensors, each of the plurality of ultrasound sensors comprising a transducer having a respective resonant frequency;

adhering the aligned substrate to a patient;

measuring a circumference of an artery using the plurality of ultrasonic sensors of the attached substrate;

measuring a blood flow velocity using the plurality of ultrasonic sensors of the attached substrate; and

mean arterial pressure is calculated using the measured circumference of the artery and the blood flow velocity.

13. The method of claim 12, wherein the circumference of the artery is measured using echo mode ultrasound imaging with the plurality of ultrasound sensors.

14. The method of claim 12, wherein the blood velocity is measured using continuous wave ultrasound with the plurality of ultrasound sensors.

15. The method of claim 12, wherein the mean arterial pressure of the patient is calculated by: the measured blood flow velocity was modeled as the stokes flow rate and normalized by the measured perimeter.

16. The method of claim 12, wherein each transducer has a frequency response that partially overlaps the frequency response of the other transducer.

17. The method of claim 12, further comprising: transmitting, using a wireless transmitter of the ultrasound measurement device, the calculated mean arterial pressure to a display system for display.

18. The method of claim 12, further comprising: iteratively calculating the mean arterial pressure and transmitting the calculated mean arterial pressure to a display system such that the display system dynamically updates a display of the mean arterial pressure.

19. A system, comprising:

an adhesive substrate configured to adhere to skin of a patient, the adhesive substrate comprising an ultrasonic measurement device comprising:

a plurality of ultrasound sensors configured to capture tomographic information of a physiological structure, each of the plurality of ultrasound sensors comprising a transducer having a respective resonant frequency, wherein each transducer has a frequency response that partially overlaps a frequency response of another transducer; and

a processing device configured to calculate a mean arterial pressure through an artery of a patient using the plurality of ultrasound sensors after the adhesive substrate is adhered to the patient; and

a wireless transmitter configured to transmit the calculated mean arterial pressure to a display system for display.

20. The system of claim 19, further comprising: the display system, wherein the display system is configured to display an interface comprising dynamic measurements of the patient's vital signs, the measurements comprising the calculated mean arterial pressure, wherein a background of the interface is configured to dynamically provide a visual indication of the patient's vital signs as normal or abnormal.

Background

Acoustic and optical imaging are commonly used for medical diagnostics. For example, x-ray transmission photography is used to visualize fractures. Also, ultrasound is used to visualize cardiac function. These visualizations facilitate patient diagnosis by providing key information to healthcare practitioners about patient physiology (physiology).

Both acoustic and optical imaging tools utilize multiple monochromatic transducers to interrogate the patient's physiology. These devices record the reflected power and receive phase of each individual transmission and map these recordings onto a two-dimensional (2D) or three-dimensional (3D) image. These images are interpreted by humans to infer characteristics such as physiology.

Disclosure of Invention

The systems and methods described herein are directed to ultrasound monitoring devices.

In one embodiment, an ultrasonic measurement apparatus includes: a plurality of ultrasound sensors configured to capture tomographic information of a physiological structure, each of the plurality of ultrasound sensors comprising a transducer having a respective resonant frequency, wherein each transducer has a frequency response that partially overlaps a frequency response of another transducer; and a processing device for controlling and processing the measurements made by the plurality of ultrasonic sensors. During capture of tomographic information of the physiological structure, each of the transducers is configured to be actuated in a time-interleaved manner to capture images of a surface of the physiological structure at a plurality of depths.

In some embodiments, the ultrasonic measurement apparatus further comprises: a substrate, wherein the substrate comprises an adhesive surface for adhering to the skin of a patient, wherein the plurality of ultrasound sensors are incorporated into the substrate. The substrate may include one or more alignment marks for aligning the device with an artery of a patient. After the substrate is aligned with the artery, the processing device is configured to calculate a mean arterial pressure through the artery using the plurality of ultrasound sensors.

The processing device may be configured to calculate a mean arterial pressure through an artery using the plurality of ultrasound sensors by performing the following: measuring a circumference of an artery using the plurality of ultrasound sensors; measuring a blood flow velocity using the plurality of ultrasonic sensors; and calculating the mean arterial pressure using the measured arterial circumference and blood flow velocity.

In some embodiments, the circumference of the artery is measured using echo mode ultrasound imaging with the plurality of ultrasound sensors. In some embodiments, the blood velocity is measured using continuous wave ultrasound with the plurality of ultrasound sensors.

In some embodiments, the ultrasonic measurement apparatus further comprises: a wireless transmitter, wherein the wireless transmitter is configured to transmit the calculated mean arterial pressure to a display system for display. In other embodiments, the ultrasound measurement device comprises a display, wherein the display is configured to display the calculated mean arterial pressure.

In some embodiments, the processing device is configured to iteratively recalculate the mean arterial pressure through the artery using the plurality of ultrasound sensors to account for beat-to-beat variations in arterial pressure.

In some embodiments, the ultrasonic measurement apparatus further comprises: a plurality of non-ultrasonic sensors, wherein each of the plurality of non-ultrasonic sensors is configured to make measurements that are correlated and normalized to ultrasonic measurements made by the plurality of ultrasonic sensors.

In one embodiment, a method comprises: aligning a substrate with an artery of a patient, wherein the aligned substrate comprises an ultrasound measurement device comprising a plurality of ultrasound sensors, each of the plurality of ultrasound sensors comprising a transducer having a respective resonant frequency; adhering the aligned substrate to a patient; measuring a circumference of an artery using the plurality of ultrasonic sensors of the attached substrate; measuring a blood flow velocity using the plurality of ultrasonic sensors of the attached substrate; and calculating mean arterial pressure using the measured arterial circumference and blood flow velocity.

In some embodiments, the circumference of the artery is measured using echo mode ultrasound imaging with the plurality of ultrasound sensors. In some embodiments, the blood velocity is measured using continuous wave ultrasound with the plurality of ultrasound sensors. In some embodiments, the mean arterial pressure of the patient is calculated by: the measured blood flow velocity was modeled as the stokes flow rate and normalized by the measured perimeter.

In some embodiments, the method further comprises: transmitting, using a wireless transmitter of the ultrasound measurement device, the calculated mean arterial pressure to a display system for display.

In some embodiments, the method further comprises: iteratively calculating the mean arterial pressure and transmitting the calculated mean arterial pressure to a display system such that the display system dynamically updates a display of the mean arterial pressure.

In one embodiment, a system comprises: an adhesive substrate configured to adhere to skin of a patient, the adhesive substrate comprising an ultrasonic measurement device comprising: a plurality of ultrasound sensors configured to capture tomographic information of a physiological structure, each of the plurality of ultrasound sensors comprising a transducer having a respective resonant frequency, wherein each transducer has a frequency response that partially overlaps a frequency response of another transducer; and a processing device configured to calculate a mean arterial pressure through an artery of a patient using the plurality of ultrasound sensors after the adhesive substrate is adhered to the patient; and a wireless transmitter configured to transmit the calculated mean arterial pressure to a display system for display. In some implementations of this embodiment, the system further includes: the display system, wherein the display system is configured to display an interface comprising dynamic measurements of the patient's vital signs, the measurements comprising the calculated mean arterial pressure, wherein a background of the interface is configured to dynamically provide a visual indication of the patient's vital signs as normal or abnormal.

Other features and aspects of the present disclosure will become apparent from the following detailed description, taken in conjunction with the accompanying drawings, which illustrate, by way of example, the features in accordance with various embodiments. This summary is not intended to limit the scope of the invention, which is defined solely by the appended claims.

Drawings

The technology disclosed herein, in accordance with one or more various embodiments, will be described in detail with reference to the following drawings. The drawings are provided for purposes of illustration only and merely depict typical or example embodiments of the disclosed technology. These drawings are provided to facilitate the reader's understanding of the disclosed technology and should not be taken to be limiting in its breadth, scope, or applicability. It should be noted that for clarity and ease of illustration, the drawings are not necessarily drawn to scale.

FIG. 1 shows a block diagram of some components of a continuous ultrasonic measurement device, according to an embodiment of the present disclosure.

Fig. 2 depicts frequency responses of three ultrasonic sensors of a continuous ultrasonic measurement device according to an embodiment of the present disclosure.

FIG. 3 depicts a cross-correlation technique for use in an ultrasonic measurement device, in accordance with an embodiment of the present disclosure.

Fig. 4 illustrates one exemplary embodiment of a bonded substrate including an integrated continuous ultrasound measurement device for monitoring vital signs including blood pressure, in accordance with embodiments of the present disclosure.

Fig. 5 illustrates an operational flow diagram of an example method of measuring mean arterial pressure using a substrate comprising a continuous ultrasound measurement device, according to an embodiment of the present disclosure.

Fig. 6A depicts an example interface that may be presented on a display as part of a patient vital measurement, according to an embodiment of the present disclosure.

Fig. 6B depicts an example interface that may be presented on a display as part of a patient vital measurement, according to an embodiment of the present disclosure.

Fig. 6C depicts an example interface that may be presented on a display as part of a patient vital measurement, according to an embodiment of the present disclosure.

FIG. 7 illustrates an example chipset that may be used to implement the architecture and methods according to various embodiments of the present disclosure.

The drawings are not intended to be exhaustive or to limit the invention to the precise forms disclosed. It is to be understood that the invention can be practiced with modification and alteration and that the disclosed techniques be limited only by the claims and the equivalents thereof.

Detailed Description

As used herein with reference to a transducer, the term "resonant frequency" generally refers to the operating frequency at which the transducer most efficiently converts electrical energy to mechanical energy. For example, in the case of a piezoelectric transducer, the term resonant frequency may refer to the operating frequency at which the piezoelectric material most easily vibrates and converts electrical energy to mechanical energy most efficiently.

Unlike free space imaging, tissue imaging suffers from poor optical and acoustic transmission and beam scattering. Many strategies have been developed to mitigate low signals in noisy tissue environments. For example, in ultrasound imaging, both the transmitter and receiver are resonance matched to maximize the receiver power and thus maximize the signal strength. This can be used for echo (echo) mode ultrasound imaging, which is a technique of recording the reflection of ultrasound waves from the surface of an object to significantly improve the contrast and resolution of ultrasound images. Furthermore, a phased array of multiple ultrasound transducers may operate at a single frequency. By varying the timing at which each transducer is pulsed, the ultrasound beam can be electronically steered through the tissue to increase the spatial component of the captured image (e.g., capture a "slice" of the tissue). However, the advantages of the above-described method (e.g., increased signal strength and high spatial components) come at the cost of limited tomography. In particular, single wavelength ultrasound is severely limited in the depth of tissue it can measure.

To address the above-described deficiencies of existing ultrasound systems and methods, the technology disclosed herein is directed to a multi-wavelength ultrasound imaging device that collects information from multiple ultrasound sensors, where each sensor has an ultrasound transducer with a unique resonant frequency. By insonating a physiological feature with multiple ultrasound sensors operating at different resonant frequencies, ultrasound emitted by multiple transducers may simultaneously penetrate various depths in a given cross-sectional area of the physiological feature (e.g., tissue). In particular, ultrasonic sensors having acoustic frequency responses may be actuated in a time-staggered manner such that each sensor may be used to image a biological surface at a unique depth. This can achieve high resolution tomographic imaging without increasing the gain or number of ultrasonic imaging sensors. Furthermore, each sensor may be actuated simultaneously with a combination of other sensors to generate higher order harmonics that allow sub-pixel feature resolution (i.e., super-resolution imaging).

FIG. 1 shows a block diagram of some components of a continuous ultrasonic measurement device 100, in accordance with an embodiment of the present disclosure. As shown, device 100 includes a plurality of ultrasonic sensors 110, a processing device 120, a machine-readable medium 130, a wireless transmitter 140, and optionally one or more non-ultrasonic sensors 150. The electrical components of the device 100 may be powered by a battery 101, the battery 101 being connected to a power circuit 102 for distributing electrical power. The battery 101 may be rechargeable (e.g., via a USB port and/or an ac/DC converter). Although a battery 101 is shown in this example, it should be understood that any suitable battery or power technology may be used to power the components of the device 100. For example, lithium ion batteries, cells, piezoelectric or vibrational energy harvesters, photovoltaic cells, alternating current/DC sources, or other similar devices may be used.

During operation, the processing device 120 may collect information from a plurality of ultrasound sensors 110 (individually referred to as "ultrasound sensors 110") to collect imaging data of a subject (e.g., a tissue of the subject). Each ultrasonic sensor 110 includes a transducer configured to convert electricity into ultrasonic waves, and vice versa. For example, the transducer may be a piezoelectric transducer that oscillates and generates ultrasonic pulses when an alternating voltage is applied. Alternatively, the transducer may be a capacitive transducer that utilizes an electrostatic field between the conductive diaphragm and the back plate to generate ultrasonic waves. The ultrasonic waves may be generated at a frequency greater than or equal to about 20 kilohertz (KHz). In an embodiment, the transducer of the ultrasonic sensor 110 may generate ultrasound at any frequency between 2 megahertz (MHz) and 20 MHz. When the transducer receives a reflected ultrasound signal (i.e., an "echo"), the ultrasound sensor 110 may generate and use an electrical signal to determine the distance to the subject being imaged.

Ultrasound waves entering the tissue may be transmitted, attenuated, or reflected. While higher frequency ultrasound may provide a higher resolution signal, it may provide poor depth penetration of the imaged tissue. Conversely, while lower frequency ultrasound may provide a lower resolution signal, it may provide better depth penetration of the imaged tissue. To overcome these limitations of conventional ultrasound imaging systems, each ultrasound sensor 110 may have a transducer configured with a unique resonant frequency. In particular, the ultrasound transducers may be selected such that their acoustic frequency responses do not overlap. By actuating the transducers in a time-staggered manner, each sensor can be used to image the surface of the sample at a unique depth. Furthermore, each transducer may be actuated simultaneously with a combination of other transducers to produce higher order harmonics that allow sub-pixel feature resolution. These principles are described by fig. 2-3, which illustrate an exemplary embodiment of three ultrasound sensors imaging a subject 300.

As shown in fig. 2, selecting partially overlapping transducers may allow for self-normalization and cross-correlation of the signals. In particular, by selecting sensor transducers with adjacent and partially overlapping frequency responses, the measurements of any pair of sensors can be normalized, thereby reducing system noise sources and significantly increasing signal integrity. Furthermore, using transducers with different resonant frequencies to interrogate the surface simultaneously, a super-resolution ultrasound image can be produced. In an embodiment, the frequency overlap between sensors may be configured to be about 200KHz or less. In an embodiment, the frequency overlap between sensors may be configured such that the frequency response range of one sensor does not overlap with the resonant frequency of another sensor. For example, as shown in FIG. 2, sensor 1 (resonant frequency f1) and sensor 2 (resonant frequency f2) partially overlap in frequency response. Further, the sensor 2 and the sensor 3 (resonance frequency f3) partially overlap in frequency response.

Fig. 3 depicts a cross-correlation technique in the ultrasonic measurement apparatus 100. As shown, cross-correlation of signals from any pair of sensors whose frequency responses overlap allows for redundant measurement of voxels (voxels). In particular, the transducers of the three sensors may be actuated in a time-staggered manner. For each actuation (e.g., frame 301), the received echoes may be measured by all three transducers (frame 302) to obtain received signals on all three transducers (frame 303). By observing the correlation of the received signals across all three sensors, the signals can be normalized. Frame 303 shows the event where the echoes from the actuation of sensor 2 are measured by all three sensors. In this case, the frequency response of the transducers 1 and 3 is convolved in the frequency domain with the received echo waveform. When deconvolved, the measurements from sensor 3 may be correlated with the measurements from sensor 2 while the measurements from sensor 1 are used to normalize the measurements of sensor 2. As shown in frame 306, sharper peaks can be seen in the signal monitored by sensor 1, and these sharper peaks can be achieved by the aforementioned normalization across frequency.

Referring again to fig. 1, processing device 120 may be configured to control the operation of the components of device 100, including ultrasonic sensors 110 and non-ultrasonic sensors 150 (discussed further below). For example, the processing device 120 may be configured to cause the ultrasound sensor 110 and/or the non-ultrasound sensor 150 to perform image acquisition. Additionally, the processing device 120 may receive, store (e.g., in the machine-readable medium 130), and/or process signal measurements received from the ultrasonic sensors 110 and/or the non-ultrasonic sensors 150. In some embodiments, the processing device 120 may also be configured to apply the above-described normalization and cross-correlation methods using the signal measurements received from the ultrasound sensor 110. The foregoing methods may be applied in accordance with instructions stored on machine-readable medium 130. In one embodiment, the processing device 120 may be implemented as a single Integrated Circuit (IC) microcontroller including a memory (e.g., machine-readable medium 130) for storing program information and data.

In the example of fig. 1, continuous ultrasound measurement device 100 includes a wireless transmitter 140 (e.g., a transceiver) configured to transmit ultrasound measurement data to a wireless receiver 240 (e.g., a transceiver) of display system 200. Depending on the ultrasound imaging application, the received ultrasound measurement data may be processed (e.g., into a format suitable for display) using processing device 210 and/or displayed using display 220. For example, as discussed further below with respect to some embodiments, the display 220 may be a component of a cardiac monitor, a mobile device, or some other suitable display device.

The wireless communication link between the wireless transmitter 140 and the wireless receiver 240 may be a radio frequency link, for exampleOrA low power consumption (LE) link,A link, a ZigBee link, or some other suitable wireless communication link. In other embodiments, data transfer between device 100 and display system 200 may be accomplished using a wired transmitter or other suitable wired interface. For example, data may be transmitted using a USB-C connector, a USB 2.x or 3.x connector, a micro-USB connector, a THUNDERBOLT connector, an ethernet cable, or the like.

In alternative embodiments, the functions of display 220 and display system 200 may be integrated into continuous ultrasound measurement device 100.

Blood pressure measurement

In some embodiments, the continuous ultrasound measurement device 100 may be used in applications of blood pressure measurement. Blood pressure is an important measure in patient care. In clinical treatment, it is usually the first vital sign measured. When emergency resuscitation is performed in emergency departments, it is often the main vital sign determining the quality of resuscitation, together with the heart rate. These measurements taken together are an indicator of shock, dehydration, hemorrhage and provide one of the only quantitative methods of assessing the quality of fluid resuscitation in patients in need of fluid. It is also a measure of whether a patient is in cardiopulmonary arrest or loss of circulation or ventilation.

While these measurements are critical for determining chronic health status, and also for measurements during code situations, current blood pressure measurement methods are still as cumbersome and cumbersome as originally developed. Currently, blood pressure is typically measured with a stethoscope and sphygmomanometer. The sphygmomanometer cuff is inflated above the systolic pressure of the patient to completely occlude a blood vessel, typically the brachial artery. The air in the sphygmomanometer cuff is then deflated and the stethoscope is used to listen for the first acoustic turbulence after the blood vessel has opened due to the pressure drop. The first sound is recorded as systolic pressure because it is related to the cuff pressure.

As the cuff continues to deflate, the turbulent sound continues until the vessel is fully open, which ultimately results in a fully linear flow. At this time, the loss of turbulent blood flow causes the korotkoff sound (turbulent flow) to stop, and the pressure at which the sound stops is recorded as the patient's diastolic pressure. The systolic and diastolic pressures are then recorded as the patient's blood pressure. While this is the "gold standard" for current blood pressure measurements, it requires multiple devices and several minutes to configure the device and make the measurement. In the case of cardiopulmonary arrest, blood pressure is critical to determining the patient's state of life, which may be several minutes invaluable.

Furthermore, the blood pressure is dynamic and changes on a beat to beat and second by second basis. The above-described conventional blood pressure measurement methods may not be able to determine a second-by-second measurement of blood pressure changes unless an intra-arterial catheter is used for invasive measurements, which is a time-consuming and painful task for the patient. The gold standard for blood pressure measurement may also be prone to errors due to variations in patient anatomy, arm size, cuff size, and room ambient noise.

To address the above-described deficiencies of existing blood pressure measurement techniques, a continuous ultrasound measurement device 100 may be used. Fig. 4 illustrates one exemplary embodiment of a bonded substrate 400 according to embodiments of the present disclosure, the bonded substrate 400 including an integrated continuous ultrasound measurement device 100 for monitoring vital signs including blood pressure. As shown, the substrate 400 includes one or more alignment lines or other markings for aligning the ultrasound sensor 110 of the integrated device 100 with an artery of a patient prior to taking an ultrasound measurement. In addition, the base plate 400 includes an adhesive (e.g., a rubber, acrylic, or acrylic hybrid adhesive) on the back that can be used to hold the base plate in place and in alignment with the patient's artery. During application, the adhesive may be exposed by peeling off the paper backing. For example, the device may be placed in the neck of a patient to measure blood flow rate and arterial dilation to measure blood pressure through the carotid artery. Similar measurements can be made on the radial or ulnar artery. With such an embodiment, the measurement of blood pressure may be non-invasive, reliable, fast, and provide continuous measurements, allowing for beat-to-beat variations. These continuous changes may be presented to the user on a display system, as discussed further below.

Fig. 5 illustrates an operational flow diagram of an example method 500 of measuring mean arterial pressure using a substrate 400 including a continuous ultrasound measurement device 100, according to an embodiment of the present disclosure. At operation 510, the substrate may be aligned with an artery of a patient and adhered to the patient using an adhesive. For example, the substrate 400 may be aligned with the patient's carotid artery and then adhered. It should be noted that by having the ultrasonic sensors 110 have partially overlapping frequency responses as described herein, the alignment requirements of the substrate 400 may be relaxed slightly.

After alignment and placement, at operation 520, the circumference of the artery may be measured with the plurality of ultrasound sensors 110. For example, the circumference may be measured using echo mode ultrasound imaging. At operation 530, the blood velocity of the patient may be individually monitored using the same ultrasound sensor 110. For example, continuous wave ultrasound may be used to monitor the blood velocity of a patient. At operation 540, the measured arterial circumference and blood velocity may be used to calculate a mean arterial pressure of the patient. For example, the mean arterial pressure of a patient may be calculated by: the measured blood velocity was modeled as Stokes flow rate and normalized by the artery circumference. In various embodiments, the processing device 120 of the continuous ultrasound measurement device 100 may perform the necessary DSP and calculations to obtain the mean arterial pressure of the patient.

At operation 550, the calculated mean arterial pressure may be transmitted to the external display system 200 (e.g., using the wireless transmitter 140) for display by the display 220. In some embodiments, the device 100 or external display system 200 may also calculate and record the patient's breathing and heart rate for display by the display 220. The display 220 may vary based on the current display capabilities of the clinician. The display 220 may also have the capability to connect to a portable mobile device or a heart monitor in a hospital environment.

Fig. 6A-6C depict example interfaces that may be presented on the display 220 as part of a patient vital measurement, according to embodiments of the present disclosure. For example, the interface may be rendered and dynamically updated in real-time by iteratively performing operation 520 and 550 of method 500. As depicted in this example, blood pressure, heart rate, respiration rate, and oxygen saturation may be displayed on the display 220. Depending on whether the value is normal or abnormal, the background may change color or otherwise change appearance. For example, as shown in fig. 6A, when all values of the vital signs are within normal limits, the background can display a first pattern or color 610 (e.g., green). As shown in fig. 6B, when a median anomaly occurs for one value of the vital sign, the background may display a second pattern or color 620 (e.g., yellow). As shown in fig. 6C, when one or more values of the vital signs are very abnormal, the background may display a third pattern or color 630 (e.g., red). In contrast to conventional techniques for presenting vital sign information (e.g., pulse oximeters showing waveforms), the image-based display of the present disclosure may provide an intuitive and silent notification method for tracking vital signs.

Referring again to continuous ultrasonic measurement device 100, in some embodiments, in addition to a multi-wavelength ultrasonic sensor, device 100 may also include one or more non-ultrasonic sensors 150 to allow for multi-mode measurements. For example, an LED light source and photodiode receiver may be integrated onto a wireless platform to measure blood oxygenation by pulse oximetry. As a specific example, a 617 nm LED light source and a 583 nm LED light source may be integrated in the device 100. By calculating the light absorbance of the 583 to 617 nanoribbons, a metric closely related to blood oxygenation can be obtained. Incident light is absorbed differently by hemoglobin depending on the oxidation state of the hemoglobin. The shift in absorption from the baseline signal allows for measurement of changes in blood oxygenation. Other example sensors that may be implemented include sensors for detecting body fluid status, cardiac ejection fraction, or other important measurements, which may be integrated into the hardware/sensor package.

In some embodiments, measurements made using non-ultrasonic sensors 150 may be correlated and normalized with ultrasonic measurements (e.g., measurements of blood velocity). By using additional modalities other than the ultrasound sensor 110 to measure the imaged physiological characteristic (e.g., blood velocity), the accuracy of the apparatus 100 may be improved.

Fig. 7 illustrates a chip set 1300 in which an embodiment of the disclosure may be implemented. Chipset 1300 may include, for example, processor and memory components incorporated into one or more physical packages. For example, a physical package includes an arrangement of one or more materials, components, and/or wires on a structural component (e.g., a backplane) to provide one or more characteristics, such as physical strength, conservation of size, and/or limitation of electrical interaction.

In one embodiment, chipset 1300 includes a communication mechanism such as a bus 1302 to communicate information between components of chipset 1300. A processor 1304 is coupled to bus 1302 to execute instructions and process information stored in a memory 1306. Processor 1304 includes one or more processing cores, each configured to execute independently. The multi-core processor supports multiprocessing within a single physical enclosure. Examples of multi-core processors include two, four, eight, or more numbers of processing cores. Alternatively or additionally, processor 1304 includes one or more microprocessors configured in series via bus 1302 to enable independent execution of instructions, pipelining, and multithreading. The processor 1304 may also perform certain processing functions and tasks with one or more specialized components, such as one or more Digital Signal Processors (DSPs) 1308, and/or one or more application-specific integrated circuits (ASICs) 1310. The DSP 1308 may generally be configured to process real-world signals (e.g., sounds) in real-time independent of the processor 1304. Similarly, ASIC1310 may be configured to perform special-purpose functions that are not readily performed by a general-purpose processor. Other specialized components to help perform the inventive functions described herein include one or more Field Programmable Gate Arrays (FPGAs) (not shown), one or more controllers (not shown), or one or more other special-purpose computer chips.

The processor 1304 and accompanying components are coupled to a memory 1306 through a bus 1302. The memory 1306 includes both dynamic memory (e.g., RAM) and static memory (e.g., ROM) for storing executable instructions that, when executed by the processor 1304, DSP 1308, and/or ASIC1310, perform the processes of the example embodiments described herein. The memory 1306 also stores data associated with or generated by the execution of the procedures.

In this document, the terms "machine-readable medium," "computer-readable medium," and similar terms are used to generally refer to volatile or non-volatile, non-transitory media that store data and/or instructions that cause a machine to operate in a specific manner. Common forms of machine-readable media include, for example, a hard disk, a solid state drive, magnetic tape, or any other magnetic data storage medium, optical disk, or any other optical data storage medium, any physical medium with patterns of holes, a RAM, a PROM, an EPROM, a FLASH-EPROM, NVRAM, any other memory chip or cartridge, and network versions thereof.

These and other various forms of computer readable media may be involved in carrying one or more sequences of one or more instructions to a processing device for execution. Such instructions contained on the medium are generally referred to as "instructions" or "code". The instructions may be grouped in the form of computer programs or other groupings. Such instructions, when executed, may enable the processing device to perform the features or functions of the present application as discussed herein.

In this context, a "processing device" may be implemented as a single processor performing processing operations or as a combination of special purpose and/or general purpose processors performing processing operations. The processing device may include a CPU, GPU, APU, DSP, FPGA, ASIC, SOC, and/or other processing circuitry.

The various embodiments set forth herein are described in terms of exemplary block diagrams, flow charts and other illustrations. It will be apparent to those of ordinary skill in the art, after reading this document, that the illustrated embodiments and their various alternatives can be practiced without limitation to the illustrated examples. For example, block diagrams and their accompanying description should not be construed as authorizing a particular architecture or configuration.

Each of the processes, methods, and algorithms described in the preceding sections may be embodied in, and executed in whole or in part automatically by, code components executed by one or more computer systems or computer processors including computer hardware. The processes and algorithms may be implemented in part or in whole in application specific circuitry. The various features and processes described above may be used independently of one another or may be used in various combinations. Various combinations and subcombinations are intended to fall within the scope of the disclosure, and certain method or process blocks may be omitted in some implementations. In addition, unless the context dictates otherwise, the methods and processes described herein are not limited to any particular order, and the blocks or states associated therewith may be performed in other suitable orders, or may be performed in parallel, or in some other manner. Blocks or states may be added to, or removed from, the disclosed example embodiments. The execution of certain operations or processes may be distributed among computer systems or computer processors, not only residing within a single machine, but also being deployed across multiple machines.

As used herein, the term "or" may be construed as inclusive or exclusive. Furthermore, singular references of resources, operations or structures should not be construed as excluding the plural. Conditional language, such as "can," "might," or "might," unless specifically stated otherwise, or otherwise understood in the context of usage, is generally intended to convey that certain embodiments include certain features, elements, and/or steps, while other embodiments do not.

Terms and phrases used in this document, and variations thereof, unless expressly stated otherwise, should be construed as open ended as opposed to limiting. Adjectives such as "conventional," "normal," "standard," "known," and terms of similar meaning should not be construed as limiting the item described to a given time period or to an item available at a given time, but instead should be read to encompass conventional, normal, or standard technologies that may be available or known now or at any time in the future. In some instances, the presence of broad words and phrases such as "one or more," "at least," "but not limited to," or other like phrases is not to be construed as meaning that a narrower case is intended or necessary in instances where such broad phrases may not be present.