Generation of Analog Continuous Wave Doppler Ultrasonic Signals in Ultrasonic Probes, and Related Systems, Devices, and Methods

Abstract

The ultrasound probe is in communication with an ultrasound system. The ultrasound probe includes a transducer array configured to generate an analog ultrasound signal. The ultrasound probe includes an analog in-phase / quadrature-phase (I / Q) mixer disposed within the ultrasound probe housing and in communication with the transducer array. The analog I / Q mixer is configured to generate an analog continuous wave (CW) Doppler signal based on the analog ultrasound signal. The ultrasound probe includes a cable coupled to the housing, the cable configured to transmit the analog CW Doppler signal from the ultrasound probe to the ultrasound system. Related devices, systems, and methods are also provided.

Description

Technical Field

[0001]

[0001] This disclosure generally relates to ultrasonic imaging such as continuous wave (CW) Doppler imaging. In particular, analog CW Doppler signals are generated using in-phase and quadrature (I / Q) mixers within an ultrasonic transducer probe.

Background Art

[0002]

[0002] Ultrasonic imaging systems are often used in medical imaging. An ultrasonic imaging system typically includes a transducer probe and a main processing system. The transducer probe includes an array of ultrasonic transducer elements. The ultrasonic transducer elements send sound waves into a patient's body, and when the sound waves are reflected by tissues and / or organs within the patient's body, signals are generated. In conventional ultrasonic applications, the timing and / or intensity of the echo signals correspond to the size, shape, and mass of the patient's tissues, organs, or other features, and an image depicting the measured tissues, organs, or other features is displayed to the user of the ultrasonic system. Some ultrasonic applications additionally employ a continuous wave (CW) Doppler imaging method to measure velocities such as the velocity of a fluid (e.g., blood flow) within a patient. The analog ultrasonic echo signals corresponding to each ultrasonic transducer element are passed from the transducer probe to the main processing system through a cable. In CW Doppler applications, the processing system displays a graphical representation of the velocities within the patient.

Summary of the Invention

Problems to be Solved by the Invention

[0003]

[0003] To transmit an analog ultrasonic echo signal from a probe to a main processing system, a connection cable includes a number of conductors and, in some instances, requires a conductor or set of conductors for each receiving ultrasonic transducer element, making the cable very thick, difficult to handle, and complex and cumbersome. Due to the many conductors within the cable, the cost of the cable is also the most costly component within an ultrasonic imaging system. The cable also has a high failure rate.

[0004]

[0004] One approach to overcoming the limitations of transmitting an analog ultrasonic signal from a probe to a processing system is to include a low-power analog-to-digital converter (ADC) within the transducer probe, perform overall or partial beamforming and / or multiplexing, and then transmit the digital signal over a reduced number of conductors. This method significantly reduces the cost, diameter, and overall operability of the cable connecting the ultrasonic imaging probe and the main processing system. However, due to the high dynamic range of CW Doppler ultrasonic signals, in some embodiments, this approach is not suitable for ultrasonic systems using a CW Doppler ultrasonic path. In particular, the low-power ADC used to convert the analog signal to a digital signal does not have sufficient dynamic range to convert the analog signal associated with CW Doppler imaging and maintain the signal with high quality.

Means for Solving the Problem

[0005]

[0005] Embodiments of the present disclosure are systems, devices, and methods for continuous wave (CW) Doppler ultrasound imaging. The ultrasound system includes a host, a probe, and a connection cable between the host and the probe. The ultrasound imaging probe includes an array of ultrasound transducers that transmit ultrasound towards a biological structure and receive waves reflected from that biological structure. The received ultrasound is used for CW Doppler imaging of velocities within a patient's biological structure. Examples of such velocities include, for example, the velocity of blood flow between chambers of the heart (e.g., between the atrium and the ventricle). In CW Doppler imaging, some ultrasound imaging systems transmit analog signals from each transducer element to the host via separate conductors and require a connection cable with many conductors. However, embodiments of the present disclosure perform some processing steps at the probe. For example, the analog signals are added and mixed within the probe by in-phase and quadrature (I / Q) mixers. In some embodiments, the CW Doppler signal is also partially or fully beamformed and / or otherwise combined within the probe before or after I / Q mixing. The mixed CW Doppler signal is transmitted to the host via the connection cable. Since the signals are added and mixed at the probe, the number of conductors within the connection cable is significantly reduced. And the cost of the cable is also significantly reduced. The complexity of the cable is also reduced. In addition, the present invention preserves the analog nature of the CW Doppler signal sent to the processing system while reducing the number of conductors required within the connection cable.

[0006]

[0006] In addition, embodiments of the present disclosure include processing components within the host system. The host system receives digital B-mode ultrasound signals and generates an image of a patient's biological structure using various processing components or circuitry. The host system receives an analog CW signal and performs further processing to generate a graphical representation of velocities (e.g., blood flow) within the biological structure.

[0007]

[0007] In an exemplary aspect, an ultrasonic probe that communicates with an ultrasonic system is provided. The ultrasonic probe includes a transducer array configured to generate an analog ultrasonic signal, an analog in-phase / quadrature phase (I / Q) mixer disposed within a housing of the ultrasonic probe and communicating with the transducer array, the analog I / Q mixer being configured to generate an analog continuous wave (CW) Doppler signal based on the analog ultrasonic signal, and a cable coupled to the housing, the cable being configured to transmit the analog CW Doppler signal from the ultrasonic probe to the ultrasonic system.

[0008]

[0008] In some embodiments, the ultrasonic probe is disposed within a housing and further includes an analog-to-digital converter (ADC) that communicates with the transducer array. The ADC is configured to convert an analog ultrasonic signal into a digital ultrasonic signal, and the cable is configured to transmit the digital ultrasonic signal to the ultrasonic system. In some embodiments, the ultrasonic probe further includes at least one of a digital beamformer or a multiplexer that communicates with the ADC. In some embodiments, the cable includes a first plurality of conductors configured to transmit the digital ultrasonic signal. In some embodiments, the cable includes a second plurality of conductors configured to transmit an analog CW Doppler signal. In some embodiments, the analog CW Doppler signal includes an I signal and a Q signal, and the second plurality of conductors includes a first conductor configured to transmit the I signal and a second conductor configured to transmit the Q signal. In some embodiments, the ultrasonic probe further includes a plurality of analog I / Q mixers disposed within the housing, and the plurality of analog I / Q mixers respectively correspond to a plurality of receiving elements of the transducer array. In some embodiments, the first conductor and the second conductor are electrically coupled in parallel to the plurality of analog I / Q mixers. In some embodiments, the individual outputs of the plurality of analog I / Q mixers are added such that the first conductor and the second conductor transmit the added output of the analog I / Q mixers. In some embodiments, the ultrasonic probe further includes a quadrature clock generator disposed within the housing and communicating with the analog I / Q mixer. In some embodiments, the ultrasonic probe further includes a plurality of conductors configured to transmit power, clock, and control signals from the ultrasonic system to the quadrature clock generator. In some embodiments, the ultrasonic probe further includes an analog beamformer disposed within the housing and communicating with the transducer array.

[0009]

[0009] In an exemplary embodiment, an apparatus is provided. The apparatus includes an ultrasonic probe and an ultrasonic system. The ultrasonic system is spaced apart from the ultrasonic probe, and a cable extends between the ultrasonic probe and the ultrasonic system.

[0010]

[0010] In one aspect, the ultrasonic system comprises a processor circuit configured to generate a graphical representation of the blood flow velocity distribution based on an analog CW Doppler signal and output the graphical representation to a display communicating with the processor circuit. In some aspects, the ultrasonic probe is configured to convert an analog ultrasonic signal into a digital ultrasonic signal, the cable is configured to transmit the digital ultrasonic signal from the ultrasonic probe to the ultrasonic system, and the processor circuit is configured to generate an ultrasonic image of the heart based on the digital ultrasonic signal and output the ultrasonic image to a display.

[0011]

[0011] In an exemplary aspect, a method is provided. The method includes generating an analog ultrasonic signal using a transducer array of an ultrasonic probe, generating an analog CW Doppler signal based on the analog ultrasonic signal using an analog in-phase / quadrature (I / Q) mixer disposed within the housing of the ultrasonic probe, transmitting the analog CW Doppler signal from the ultrasonic probe to an ultrasonic system spaced apart from the ultrasonic probe by a cable coupled to the housing, generating a graphical representation of the blood flow velocity based on the analog CW Doppler signal using a processor circuit of the ultrasonic system, and outputting the graphical representation to a display communicating with the processor circuit.

[0012]

[0012] Further aspects, features, and advantages of the present disclosure will become apparent from the following detailed description.

[0013]

[0014] Exemplary embodiments of the present disclosure will be described with reference to the accompanying drawings.

Brief Description of the Drawings

[0014]

Figure 1

[0015] FIG. 1 is a schematic diagram of an ultrasonic imaging system according to an aspect of the present disclosure.

Figure 2

[0016] FIG. 2 is a schematic diagram of a processor circuit according to an aspect of the present disclosure.

Figure 3

[0017] FIG. 3 is a schematic diagram showing an exemplary circuitry of an ultrasonic imaging probe according to an aspect of the present disclosure.

Figure 4

[0018] FIG. 7 is a schematic diagram showing an exemplary circuitry of an ultrasonic imaging host system according to an aspect of the present disclosure.

Figure 5A

[0019] FIG. 11 is a schematic diagram showing an exemplary ultrasonic transducer array according to an aspect of the present disclosure.

Figure 5B

[0020] FIG. 15 is a schematic diagram showing an exemplary ultrasonic transducer array according to an aspect of the present disclosure.

Figure 6

[0021] FIG. 19 is a flowchart of an ultrasonic imaging method according to an aspect of the present disclosure.

DETAILED DESCRIPTION

[0015]

[0022] For the purpose of promoting an understanding of the principles of the present disclosure, reference is made to the embodiments illustrated in the drawings, and specific language is used to describe the same. It should, however, be understood that no limitation of the scope of the present disclosure is thereby intended. Alternative forms and further modifications of the principles of the present disclosure, as well as such further applications of the devices, systems, and methods described, are fully contemplated by those of ordinary skill in the art associated with the present disclosure and are to be included within the present disclosure. In particular, features, components, and / or steps described with respect to one embodiment may be combined with features, components, and / or steps described with respect to other embodiments of the present disclosure. However, for the sake of brevity, numerous repetitions of these combinations are not separately described.

[0016]

[0023] Figure 1 is a schematic diagram of an ultrasonic imaging system 100 according to an aspect of the present disclosure. The system 100 is used to scan a region, area, or volume of a patient's body. The system 100 is referred to as a device in some examples. The system 100 includes an ultrasonic imaging probe 110 that communicates with a host 130 over a communication interface or link 150. The probe 110 emits ultrasonic waves at a high level towards a biological structural object 105 (e.g., a patient's body) and receives ultrasonic echoes reflected from the object 105. The probe 110 transmits an electrical signal representative of the received echoes towards the host 130 over the link 150 for processing and image display. The probe 110 may be in any suitable form for imaging various body parts of the patient while being positioned inside or outside the patient's body. For example, the probe 110 may be in the form of a handheld ultrasonic scanner or a patch-based ultrasonic device. In some embodiments, the probe 110 is an intravascular probe such as a catheter, a transesophageal echocardiography (TEE) probe, and / or any other suitable endocavitary probe. The probe 110 includes a transducer array 112, various circuit networks 114, and a communication interface 122.

[0017]

[0024] The transducer array 112 emits ultrasonic signals towards the object 105 and receives echo signals reflected from the object 105 towards the transducer array 112. The transducer array 112 includes acoustic elements arranged in a one-dimensional (1D) array, a 1.X-dimensional array, or a two-dimensional (2D) array. The acoustic elements are referred to as transducer elements. Each transducer element emits ultrasonic waves towards the object 105 and receives an echo when the ultrasonic waves are reflected from the object 105. For example, the transducer array 112 includes M transducer elements that create M analog ultrasonic echo signals 160. In some embodiments, M is approximately 2, 16, 64, 128, 192, 1000, 5000, 9000, and / or any other suitable value that may be larger or smaller.

[0018]

[0025] The circuit network 114 positioned within the probe 110 can be of any suitable type and provides multiple functions. For example, the circuit network 114 includes resistors, capacitors, transistors, inductors, relays, clocks, timers, or any other suitable electrical components incorporated into integrated circuits. Additionally, the circuit network 114 is configured to support analog signals and / or digital signals that are transmitted to or from the transducer array 112 and / or the probe 110. In some embodiments, the circuit network 114 includes, among other components, an analog front end (AFE), an analog-to-digital converter (ADC), a multiplexer (MUX), and an encoder. The circuit network 114 includes hardware components, software components, and / or a combination of hardware components and software components.

[0019]

[0026] The communication interface 122 is coupled to the circuit network 114 via L signal lines. In some embodiments, the circuit network 114 reduces the number of required lines from M signal lines to L signal lines. This is achieved by any suitable method using any suitable components. For example, a MUX, a beamformer, or other components are used to reduce the M required signal lines from the transducer array 112 to the L signal lines 166. In the embodiment of FIG. 1, L is smaller than M. The communication interface 122 is configured to transmit the L signals 166 to the host 130 via the communication link 150. As will be described in more detail herein, the communication link 150 includes L data lanes for transferring the digital signal 168 to the host 130. The communication interface 122 includes a hardware component, a software component, or a combination of a hardware component and a software component configured to generate the signal 168 and carry information from the L signals 166 for transmission on the communication link 150. The signal 168 is a digital signal, an analog signal, or a combination of a digital signal and an analog signal.

[0020]

[0027] Host 130 is any suitable computing device and display device, such as a workstation, personal computer (PC), laptop, tablet, mobile phone, or patient monitor. Host 130 is referred to as an ultrasonic system or an ultrasonic host system. In some embodiments, host 130 is disposed on a movable cart. In host 130, communication interface 140 receives digital signal and / or analog signal 168 from communication link 150. Communication interface 140 includes a hardware component, a software component, or a combination of a hardware component and a software component. The communication interface is substantially similar to communication interface 122 within probe 110.

[0021]

[0028] The circuit network 134 located within the host 130 may be of any suitable type and provide any suitable function. For example, the circuit network 134 includes resistors, capacitors, transistors, inductors, relays, clocks, timers, processing components, memory components, or any other suitable electrical components incorporated into integrated circuits. In addition, the circuit network 134 is configured to support analog signals and / or digital signals transmitted to or from the probe 110. The circuit network 134 is configured to process the signal 168 received from the probe 110. For example, the circuit network 134 expands the L signal lines received from the probe 110 to the original M signal lines corresponding to specific transducer elements or groups / patches of transducer elements within the transducer array 112. In addition, the circuit network 134 includes a central processing unit (CPU), a digital signal processor (DSP), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a controller, a field programmable gate array (FPGA), another hardware device, a firmware device, or any combination thereof. The circuit network 134 is also implemented as a combination of computing devices, for example, a combination of a DSP and a microprocessor, a combination of a GPU and a microprocessor, a combination of multiple microprocessors, a combination of one or more microprocessors together with a DSP core, or any other such configuration. The circuit network 134 is configured to generate an image signal 174 for display to the user and / or perform image processing and image analysis for various diagnostic modes or types of ultrasound (B-mode, CW Doppler, etc.). For example, the circuit network 134 is configured to process the received digital ultrasound signal to generate an ultrasound image of a patient's biological structure (e.g., the heart) and output the ultrasound image to the display 132. The circuit network 114 includes hardware components, software components, and / or a combination of hardware components and software components.

[0022]

[0029] The display unit 132 is coupled to the circuit network 134. The display unit 132 includes a monitor, a touch screen, or any suitable display. The display unit 132 is configured to display images and / or diagnostic results processed by the circuit network 134. The host 130 further includes a keyboard, a mouse, a touch screen, or any suitable user input component configured to receive user input for controlling the system 100.

[0023]

[0030] FIG. 1 is described in the context of transmitting a digital ultrasonic echo signal from the probe 110 to the host 130 for display, but the host 130 can generate signals for transmission to the probe 110. For example, a power signal, a signal for controlling the probe 110 (e.g., exciting transducer elements in the transducer array 112 to emit energy) is transmitted by the host 130 to the probe 110 over the communication link 150.

[0024]

[0031] Figure 2 is a schematic diagram of a processor circuit 210 according to an aspect of the present disclosure. The processor circuit 210 is implemented in the probe 110, the host system 130 of FIG. 1, or any other suitable location. One or more processor circuits 210 are configured to perform the operations described herein. The processor circuit 210 includes additional circuitry or electronic components such as those described herein. In one example, the processor circuit 210 communicates with the transducer array 112, the circuit network 114, the communication interface 122, the communication interface 140, the circuit network 134, and / or the display 132, and any other suitable components or circuits within the ultrasonic system 100. In some embodiments, one or more components of the processor circuit 210 form at least a portion of the circuit network 114 or the circuit network 134. In some embodiments, one or more components of the circuit network 114 or the circuit network 134 form at least a portion of the processor circuit 210. In some examples, a separate processor circuit 210 is implemented in the probe 110 and a separate processor circuit 210 is implemented in the host 130. As shown, the processor circuit 210 includes a processor 260, a memory 264, and a communication module 268. These elements communicate with each other either directly or indirectly, such as via one or more buses for example.

[0025]

[0032] The processor 260 includes a CPU, a GPU, a DSP, an application specific integrated circuit (ASIC), a controller, an FPGA, another hardware device, a firmware device, or any combination thereof configured to perform the operations described herein. The processor 260 may also be implemented as a combination of computing devices, such as, for example, a combination of a DSP and a microprocessor, a combination of multiple microprocessors, a combination of one or more microprocessors in conjunction with a DSP core, or any other such configuration.

[0026]

[0033] Memory 264 includes cache memory (e.g., the cache memory of processor 260), random access memory (RAM), magnetoresistive memory (MRAM), read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), flash memory, solid-state memory devices, hard disk drives, other forms of volatile and non-volatile memory, or combinations of various types of memory. In one embodiment, memory 264 includes a non-transitory computer-readable medium. Memory 264 stores instructions 266. When executed by processor 260, instructions 266 include instructions that cause processor 260 to perform the operations described herein with reference to probe 110 and / or host 130 (FIG. 1). Instructions 266 are also referred to as code. The terms "instructions" and "code" should be construed broadly to include any type of computer-readable statement. For example, the terms "instructions" and "code" refer to one or more programs, routines, subroutines, functions, procedures, etc. "Instructions" and "code" include a single computer-readable statement or multiple computer-readable statements.

[0027]

[0034] Communication module 268 includes any electronic circuitry and / or logic circuitry for facilitating direct or indirect communication of data between processor circuit 210, probe 110, display 132, and / or display 266. In this regard, communication module 268 is an input / output (I / O) device. In some examples, communication module 268 facilitates direct or indirect communication between various elements of processor circuit 210, probe 110 (FIG. 1), and / or host 130 (FIG. 1).

[0028]

[0035] FIG. 3 is a schematic diagram showing an exemplary circuitry of an ultrasonic imaging probe according to an aspect of the present disclosure. FIG. 3 provides a more detailed view of the probe 110 of the system 100, including a transmission path from the probe 110 to the host 130 and a transmission path from the host 130 to the probe 110.

[0029]

[0036] As shown in FIG. 3, the probe 110 further includes a housing 305, an optional analog beamformer 314, L circuit blocks 310 (for example, including L transmit / receive switches (T / R switches) 316, a transmit pulsar 318, a preamplifier 319, an analog-to-digital converter (ADC) 320, a quadrature phase clock generator 380, in-phase / quadrature phase mixers 382, 384), a combiner 322, and / or a serializer and high-speed current mode logic (CML) 324. The probe 110 includes a plurality of circuit network blocks 310, and the blocks respectively correspond to different signal channels associated with a group or sub-array of transducer elements of the transducer array 112. A connection cable 390 is positioned between the probe 110 and the host 130 to establish signal communication. In this regard, the probe 110 and the host 130 are separated from each other. The connection cable 390 extends between the probe 110 and the host 130. The circuitry within the host 130 transmits signals to the circuitry within the probe 110 via the cable 390. The circuitry within the probe 110 transmits signals to the circuitry within the host 130 via the cable 390. The cable 390 includes a plurality of signal lines including conductors, twisted pairs, coaxial cables, twinaxial cables, and / or any other suitable communication conduction path for transferring data. The cable 390 includes a power conductor 394 for transmitting power from the host 130 to the probe 110. The cable 390 also includes a control signal line 392 and a clock line 391 for transmitting control signals and clock signals from the host 130 to the probe 110, respectively. The cable 390 also includes one or more digital signal lines 396 for transmitting digital ultrasonic signals from the probe 110 to the host 130, and I / Q signal lines 398, 399 for transmitting analog CW Doppler signals from the probe 110 to the host 130. The housing 305 is any suitable enclosure made of any suitable material and houses any or all of the components described herein. The cable 390 is coupled to the housing 305.

[0030]

[0037] The communication path from probe 110 to host 130 starts with converter array 112 shown in FIG. 3. Converter array 112 is coupled to housing 305. Converter array 112 includes M converter elements. As described above, in some embodiments, M is any suitable number, and the converter elements are of any suitable type in any suitable arrangement configuration. Converter array 112 generates an analog electrical signal representative of an analog ultrasonic signal or ultrasonic echoes received by one or more converter elements for any suitable imaging type (e.g., B-mode imaging, CW Doppler imaging, etc.). In CW Doppler imaging, while one or more of converter array 112 are continuously emitting ultrasonic energy, one or more other elements of converter array 112 are continuously receiving ultrasonic echoes (based on the emitted ultrasonic energy). For example, half of the acoustic elements in converter array 112 can transmit while half of the acoustic elements in converter array 112 receive.

[0031]

[0038] The transducer array 112 communicates with the analog beamformer 314 via M signal lines. The analog beamformer 314 is used to reduce the signal lines from the transducer array 112 to the rest of the network 114 (FIG. 1) within the probe 110. For example, in some embodiments, the analog beamformer 314 delays and sums the signals received from the transducer array 112 to create a small subset. The analog beamformer 314 is a receive beamformer and / or a transmit beamformer. In embodiments where the analog beamformer is a transmit beamformer, the analog beamformer 314 includes or communicates with a high voltage pulse generation circuit. In other embodiments, for example, in embodiments where the transducer array 112 is a one-dimensional array of transducer elements or the number of transducer elements is otherwise reduced, the analog beamformer 314 is not necessarily required or included within the probe 110. In some embodiments where the transducer array 112 is a one-dimensional array or the number of transducer elements is otherwise reduced, the analog beamformer 314 may still be included within the probe 110.

[0032]

[0039] The analog beamformer 314 communicates with a plurality of T / R switches 316 via a reduced number of signal lines (e.g., L signal lines). The probe 110 includes one T / R switch 216 for each transducer element of the array 112, or for each group / patch of transducer elements. The T / R switch 316 is configured to switch positions between different transmit signal paths and receive signal paths. For example, in the position of the transmit path, the T / R switch 316 transmits a high-voltage activation signal from the pulsar 318 to one or more elements of the transducer array 112 to activate one or more elements of the transducer array 112 to emit ultrasonic energy. In the receive mode, the T / R switch 316 transmits a received signal corresponding to the reflected wave received by one or more transducer elements of the transducer array 112 to the preamplifier 319. The T / R switch 316 communicates with the host 130 via the control line 392 and receives commands regarding switching of various signal paths through the control line 392. The T / R switch 316 also communicates with the host 130 by any other suitable conductor or method.

[0033]

[0040] The probe 110 additionally includes a transmit pulsar 318. The transmit pulsar 318 receives a command signal generated by the host 130. In response to the command signal, the transmit pulsar 318 generates an electrical excitation pulse that is timed such that the transducer array 112 creates an acoustic transmit wavefront with desired or specified focus characteristics.

[0034]

[0041] The probe 110 includes L preamplifiers 319. The preamplifier 319 amplifies the signal received from the T / R switch 316 to improve the quality of the received signal, for example, by reducing the noise floor. In some embodiments, the number of transmit pulsars 318 is equal to the number of transmit pulsars 318 and the number of T / R switches 316. For example, each T / R switch 316 is configured to receive data from one pulsar 318 and also transmit data from the transducer array 112 to one preamplifier 319.

[0035]

[0042] The received signal path is the same from the transducer array to the preamplifier 319 for both the CW Doppler imaging data and other imaging data (e.g., B-mode imaging data). In the preamplifier 319, the received signal path branches at the probe 110 such that it includes different parallel paths for the CW Doppler imaging data and other imaging data. For the signal path for other imaging data, such as B-mode imaging data, each preamplifier 319 communicates with an ADC 320. The ADC 320 is configured to convert an analog ultrasonic echo signal into a digital ultrasonic echo signal. In this regard, the ultrasonic probe 110 generates a digital ultrasonic signal from an analog ultrasonic signal and transmits the digital ultrasonic signal to the host 130. For example, the ADC 320 receives an analog ultrasonic echo signal from the transducer array 112 via the T / R switch 316 and the preamplifier 319 and converts them into digital ultrasonic echo signals. The digital ultrasonic echo signals include digital samples representing the waveform corresponding to the analog ultrasonic echo signal. The ADC 320 employs a successive approximation ADC architecture to achieve high performance and low power consumption, thus keeping the total power loss of the probe 110 within the thermal budget of the probe 110. However, any suitable ADC architecture may be used for the ADC 320.

[0036]

[0043] Each ADC 320 communicates with a combiner 322. The combiner 322 represents a network of circuits capable of reducing the total signal lines received from the ADC 320 and also capable of reducing the number of signal lines necessary to transmit data to the host 130. The combiner 322 reduces the number of signal lines by any suitable method. In some embodiments, combiner 322 includes an adder node. Combiner 322, as well as any other suitable components or circuitry within system 100, includes features similar to those described in U.S. Patent Application No. 16 / 329,433, entitled "ULTRASOUND PROBE WITH MULTILINE DIGITAL MICROBEAMFORMER," filed on February 28, 2019, and / or U.S. Provisional Patent Application No. 62 / 631,549, entitled "DIGITAL ULTRASOUND CABLE AND ASSOCIATED DEVICES, SYSTEMS, AND METHODS," filed on February 16, 2018. Both of these documents are hereby incorporated by reference in their entirety. Combiner 322 is a multiplexer and / or a digital beamformer. In some embodiments, combiner 322 may be a multiplexer and may multiplex the data received from ADC 320 onto a high-speed serial link and then transmit the data to host 130 for processing. In some embodiments, combiner 322 is a digital beamformer that performs the second step of beamforming (delaying and adding of signals) after the first step of beamforming is completed by analog beamformer 214. Combiner 322 communicates with a serializer and high-speed current mode logic (CML) 324. Serializer / CML 324 reconstructs the lines received from combiner 322 and / or ADC 320 into a high-rate serial data stream. In some embodiments, serializer / CML 324 operates at a higher data rate than other circuitry within probe 110. For example, the serial data stream operates at 160 MHz, while other circuitry within the ultrasound signal path operates at 20 MHz. Serializer / CML 324 operates in a manner similar to the serializer disclosed in U.S. Provisional Patent Application No. 62 / 631,549, entitled "DIGITAL ULTRASOUND CABLE AND ASSOCIATED DEVICES, SYSTEMS, AND METHODS," filed on February 16, 2018, which is hereby incorporated by reference in its entirety.Accordingly, in one of the signal paths of probe 110, digital ultrasonic data (e.g., B-mode data) is transmitted from probe 110 to host 130 via conductor 396. Conductor 396 is a twisted pair of conductors, a coaxial cable, a twinaxial cable, and / or any other suitable signal conduction path. Generally, one or more conductors transmit digital ultrasonic signals from probe 110 to host 130.

[0037]

[0044] In a parallel CW Doppler imaging path, ultrasonic probe 110 generates an analog CW Doppler signal from an analog ultrasonic signal and transmits the analog CW Doppler signal to host 130. Circuit network block 310 of ultrasonic probe 110 includes quadrature clock generator 380. Each quadrature clock generator 380 communicates with analog I / Q mixers 382, 384. Analog I / Q mixers 382, 384 are disposed within housing 305 and communicate with transducer array 112. I / Q mixers 382, 384 generate an analog CW Doppler signal within probe 110 that is then transmitted to host 130. In particular, I / Q mixers 382, 384 generate an analog baseband quadrature output. FIG. 3 depicts I mixer 382, Q mixer 384, and quadrature clock generator 380 located within probe 110. In each circuit block 310 or ultrasonic channel, an individual I / Q mixer generates a CW Doppler signal for ultrasonic data corresponding to an associated group or subarray of acoustic elements. The CW Doppler signals from each circuit block 310 are converted to baseband and added together prior to being transmitted to host 130. This reduces the number of conductors required to transmit CW Doppler signal data as compared to the case where different conductors would be required for each ultrasonic channel or circuit block 310. In some embodiments, the analog CW Doppler signal is transmitted from probe 110 to host 130 via two signal lines (I signal line 398 corresponding to the summed output of I mixer 382, and Q signal line 399 corresponding to the summed output of Q mixer 384). Stated another way, the outputs of I mixer 382 and Q mixer 384 are electrically connected in parallel to create two signal lines, I signal line 398 and Q signal line 399. In this manner, I signal line 398 carries the summed output of I mixer 382 within housing 305, and Q signal line 399 carries the summed output of Q mixer 384 within housing 305.

[0038]

[0045] The quadrature phase clock generator 380 includes two outputs, one of which communicates with the I mixer 382 and the other communicates with the Q mixer 384. The quadrature phase clock generator 380 creates a delay difference between the output of the I mixer 382 and the output of the Q mixer 384. The delay difference of the Q mixer 384 is equal to a quarter clock phase from the clock signal of the I mixer 382, whereby the I mixer 382 creates a signal of the same phase and the Q mixer 384 creates a signal of the quadrature phase. In some embodiments, the quadrature phase clock generator 380 generates a signal substantially similar to a rectangular wave. The quadrature phase clock generator 380 includes any suitable electrical components for generating a phase difference between the I mixer 382 and the Q mixer 384. For example, the quadrature phase clock generator 380 includes D flip-flops triggered by one or more edges, or any other suitable flip-flop, inverters such as tri-state inverters, or any other suitable electrical components. The quadrature phase clock generator 380 receives power, a clock, and control signals from the host 130 through connections 394, 391, and 392, respectively.

[0039]

[0046] An I mixer 382 is positioned within the probe 110 with one I mixer 382 for each circuit block 310. In some embodiments, the I mixer 382 is a multiplication mixer. In other embodiments, the I mixer 382 is any suitable mixer of any particular type. The I mixer 382 includes two inputs. One input communicates with the output of the preamplifier 319 within the circuit network block 310 and receives an ultrasonic signal. The other input communicates with the output of the quadrature phase clock generator 380. The I mixer 382 multiplies the signal received by the transducer array 112 with the signal received from the quadrature phase clock generator 380 and outputs the result. Thus, the output signal from the I mixer 382 corresponds to the sum and difference of the two input signals.

[0040]

[0047] Similar to the I mixer 382, the Q mixer 384 is also positioned within the probe 110 with one Q mixer 384 per circuit block 310. The Q mixer 384 may also be a multiplication mixer or any other suitable type of mixer. The Q mixer 384 is substantially similar to the I mixer 382. However, the Q mixer 384 differs from the I mixer 382 in that it receives a phase-shifted signal from the quadrature phase clock generator 380. However, similar to the I mixer 382, the Q mixer 384 also multiplies two inputs, one input corresponding to (receiving the electrical signal generated by the transducer array 112 in response to the received echo) the output of the preamplifier 319, and the other input communicating with the output of the quadrature phase clock generator 380. Similar to the I mixer 382, the Q mixer 384 also reduces the CW Doppler signal content received from the transducer array 112 to baseband prior to transmitting it to the host 130.

[0041]

[0048] As described above, the plurality of I mixers 382 and Q mixers 384 are positioned within the probe 110. In some embodiments, an I mixer 382 is present in each circuit block 310, and a Q mixer 384 is present in each circuit block 310. In some embodiments, the outputs from each I mixer 382 and each Q mixer 384 are transmitted from the probe 110 to the host 130 via a twisted pair, coaxial cable, twinaxial cable, and / or other suitable conductors. In other embodiments, as shown in FIG. 3, the outputs of all the I mixers 382 within the probe 110 are added to a single twisted pair 398, coaxial cable, twinaxial cable, or other type of wiring corresponding to the I mixer output signal before being transmitted to the host 130. Generally, one or more conductors transmit the I signal from the probe 110 to the host 130. Similarly, the outputs of all the Q mixers 384 within the probe 110 are added to a single twisted pair 399, coaxial cable, twinaxial cable, or other type of wiring corresponding to the Q mixer output signal before being transmitted to the host 130. Generally, one or more conductors transmit the Q signal from the probe 110 to the host 130. The I signal line 398 may be a twisted pair or any other suitable conductor such as a coaxial cable or twinaxial cable. The Q signal line 399 is substantially similar to the I signal line 398. Since the I / Q outputs are connected in parallel respectively, only one signal conduction path (e.g., a twisted pair, coaxial cable, twinaxial cable, and / or any suitable conductor) is required to carry the added I signal on the I signal line 398, and only one signal conduction path (e.g., a twisted pair, coaxial cable, twinaxial cable, and / or any suitable conductor) is required to carry the added Q signal on the Q signal line 399. Advantageously, this reduces the number of analog CW Doppler signal carrier lines within the cable 390. For example, the CW Doppler signal lines for each ultrasonic channel (each circuit block 310) are undesirable bulk and costly with respect to the cable 390, but this is advantageously avoided.

[0042]

[0049] Probe 110 transmits digital ultrasonic data via conductor 396 and transmits an analog CW Doppler signal via conductors 398 and 399. Advantages of the present disclosure include maintaining the analog nature of the CW Doppler signal transmitted from probe 110 to host 130. Transmitting the analog CW Doppler signal to host 130 prevents artifacts in the data inherent to some digital conversion processes. As a result, the analog CW Doppler signal retains its original signal quality and leads to better quality images and / or flow velocity measurements. Additionally, the analog CW Doppler signal is processed in the host using similar components or techniques as existing systems, thereby reducing the cost of implementation.

[0043]

[0050] FIG. 4 is a schematic diagram showing an exemplary circuitry of an ultrasonic imaging host system 130 according to an aspect of the present disclosure. FIG. 4 provides a more detailed view of host 130 of system 100, including the transmission path from probe 110 to host 130 and the transmission path from host 130 to probe 110. As shown in FIG. 4, host 130 includes a controller 452, a power supply 454, a B-mode processing circuit block 410, a CW Doppler processing circuit block 420, a fast Fourier transform (FFT) processing block 462, a conditioning block 464, and a display 466.

[0044]

[0051] The controller 452 within the host 130 controls the operation of the probe 110 and / or any number of components within the host 130. For example, the controller 452 controls the combiner 322 and / or the serializer / CML 324 (FIG. 3). The controller 452 generates control data for operating the transducer elements in the transducer array 112, for example for generating ultrasonic waves. The controller 452 further controls the analog beamformer 314, the T / R switch 316, the pulsar 318, the preamplifier 319, and the quadrature phase clock generator 380 (FIG. 3). The controller also communicates with components within the B-mode processing circuitry block 410 and / or the CW Doppler processing circuitry block 420, including an encoder, a serialize and / or deserialize component, a transmitter, or any other suitable component within the host 130. In some embodiments, the controller 452 may be a processor circuit or a part of a processor circuit. The controller 452 may be a part of the processor circuit 210 shown in FIG. 2. The control line 392 communicates with the controller within the host 130 and provides signals for controlling the components within the probe 110. In some embodiments, the control line 392 and / or the clock line 391 may be a twisted pair. In other embodiments, the control line 392 and / or the clock line 391 are conductors, coaxial cables, twinaxial cables, and / or any other suitable signal communication conduction path for transmitting data signals. In some embodiments, the data transmitted via the control line 392 may be 800 Mbs data or data of any frequency or type. The signals transmitted from the host 130 to the probe 110 via the control line 392 and / or the clock line 391 may be analog signals or digital signals. When a digital command signal is transmitted, the data is transmitted via the data line 292 at any suitable bit rate, including values such as between 400 Mbit / s and 8 Gbit / s and other suitable values that may be higher or lower than 2.4 Gbit.

[0045]

[0052] Power supply 454 provides power to host 130 and probe 110 (e.g., any suitable component within probe 110 or host 130). Power line 394 communicates with power supply 454 at any suitable location within host 130 or with respect to other components. Power line 394 provides power to various components within probe 110.

[0046]

[0053] Processing circuit block 410 receives digital ultrasonic signals via signal line 396. Processing circuit block 410 includes any suitable components used to process digital ultrasonic data, generate ultrasonic images, and output display data for display on display 466 to a user of ultrasonic system 100. In this regard, processing circuit block 410 is implemented as a hardware component, a software component, and / or a combination of a hardware component and a software component. For example, circuit block 410 includes an encoder, a serializer component, a deserialzer component, a transmitter, a decoder, a multiplexer, a demultiplexer, a beamformer, or any other suitable component. Circuit block 410 also includes a signal processing component, a scan converter component, a controller, or other components. Circuit block 410 is configured to display to a user a rendering of tissue, organs, or other structures within a patient's biological structure. Processing circuit block 410 is used to process digital B-mode ultrasonic imaging signals. In other embodiments, processing circuit block 410 represents a circuit that may be used for a processing circuit for any suitable ultrasonic imaging type (e.g., B-mode imaging, 3D / 4D imaging, M-mode imaging, color flow Doppler imaging, or any other suitable form or type of ultrasonic imaging).

[0047]

[0054] The CW Doppler processing circuit block 420 receives an analog CW Doppler signal via signal lines 398 and 399. The CW Doppler processing circuit block 420 includes a plurality of high-pass filters (HPFs) 432, an anti-aliasing low-pass filter (LPF) 430, and an analog-to-digital converter (ADC) 426. In this regard, the CW Doppler processing circuit block 420 includes the HPF 432, the LPF 430, and the ADC 426 for each of the I signal conduction path and the Q signal conduction path. The HPF 432 is referred to as a wall filter. The HPF 432 and the LPF 430 are analog components.

[0048]

[0055] In the illustrated embodiment, the HPF or wall filter 432 acts on the analog CW Doppler signal. The HPF 432 is positioned either within the probe 110 or within the host 130 as shown in FIG. 4. One HPF 432 communicates with the added output of the I mixer 382 via the I signal line 398, and an additional HPF 432 communicates with the added output of the Q mixer 384 via the Q signal line 399. The wall filter 432 includes additional circuitry within the host 130. The wall filter 432 also includes an operational amplifier. The HPF 432 filters out low Doppler signals corresponding to arterial walls within the patient or any other static tissue. The HPF 432 additionally filters out high-amplitude low-frequency content due to movement within the patient such as a heartbeat, general patient or probe movement, or other movement. In some embodiments, the HPF 432 includes an aggressive filter.

[0049]

[0056] After the signal is processed through HPF432, LPF430 may be used to remove high-frequency energy. If not, such energy will be aliased into the passband by the sampling function of analog-to-digital converter 426. In this regard, the CW Doppler ultrasonic signal is obtained when high-frequency ultrasonic energy is emitted by transducer array 112 and propagates through the patient's biological structure. The ultrasonic echo is an echo with a frequency slightly higher or lower than the emitted ultrasonic energy, based on the emitted ultrasonic energy received by transducer array 112, and corresponds to a moving fluid such as blood flow. In this case, the relevant information about the CW Doppler imaging extracted from the ultrasonic signal is the difference between the transmitted ultrasonic energy and the received ultrasonic energy. The output of I mixer 382, which corresponds to the sum and difference of the inputs of I mixer 382, is then filtered by LPF430 to remove the high-frequency content corresponding to the sum, leaving only the low acoustic level frequency or baseband frequency for additional processing. This filtering may be performed within probe 110, within circuit network block 310, or after the signal is transmitted to host 130 within host 130. The output of Q mixer 384 is also filtered by LPF430, like I mixer 382. This filtering may be performed within probe 110, within circuit network block 310, or after the signal is transmitted to host 130 within host 130.

[0050]

[0057] Following the LPF 430, one or more analog-to-digital converters (ADCs) 426 are utilized to convert the analog CW Doppler signal into a digital CW Doppler signal. In some embodiments, the ADC 426 may be positioned after the LPF 430 and before the FFT 462. However, in other embodiments, the ADC 426 may be positioned at any other location within the host 130 along the signal chain. For example, the ADC 426 may be positioned before the HPF 432, between the HPF 432 and the LPF 430, or at any other suitable location. Thus, all circuitry behind the position of the ADC 426 is either digital implementation circuitry or implemented via software and / or hardware circuitry, while the processing circuitry before the position of the ADC 426 in the signal chain is analog implementation circuitry. Therefore, in the embodiment illustrated in FIG. 4, the HPF 432 and the LPF 430 are analog components. In other embodiments, the HPF 432 and the LPF 430 are digital components.

[0051]

[0058] The fast Fourier transform (FFT) 462 is applied to the signal data output from the CW Doppler signal processing circuitry block 420 to create a Doppler spectrum associated with the speed of movement within the patient. Following the FFT 462, the signal data is further processed at conditioning 464 and then output for display to the user by the display 466. In this regard, in CW Doppler imaging, a graphical representation of the distribution of blood flow velocity is output by the display 466. It is fully contemplated that any suitable form of data processing may be applied to the signal data at this or other steps in the circuitry of the present invention. For example, the host 130 may apply additional data processing techniques to enhance the quality of the signal data and to identify or emphasize various characteristics or aspects of the signal data.

[0052]

[0059] FIG. 4 further depicts a connection cable 390 positioned between the probe 110 and the host 130. The cable 390 includes a plurality of signal lines including conductors, twisted pairs, coaxial cables, twinaxial cables, or any other suitable communication conduction path for transferring data. In some embodiments, the cable can be replaced with an optical interface or a wireless interface. For example, the cable 390 includes the control line 392, the power line 394, the clock line 391, and the plurality of signal lines 396 discussed above. The plurality of signal lines 396 corresponds to the reduced number of signal lines output from the combiner 322 and / or the serializer / CML 324. In some embodiments, the signal line 396 includes only a single signal line. In other embodiments, the signal line 396 includes a plurality of signal lines. The cable 390, and any corresponding cables such as the control line 392, the clock line 391, the signal line 396, the power line 394, and / or the I mixer line 398 and the Q mixer line 399 surrounded by the cable 390, may be of any suitable length and / or may be a flexible and elongated member. For example, the cable 390 and all associated conductors can be 1 meter, 2 meters, 3 meters in length, longer, or any suitable length therebetween.

[0053]

[0060] In some embodiments, the B processing network block 410 and the CW Doppler processing network block 420 are composed of separate components and separate signal paths. In some embodiments, a component or set of components within the processing network block 410 is shared with any other network or component within the CW Doppler processing network block 420 or the host 130.

[0054]

[0061] In some embodiments, the B-mode processing circuitry block 410 may be a processor circuit or a part of a processor circuit. The B-mode processing circuitry block 410 may be a part of the processor circuit 210 shown in FIG. 2. The B-mode processing circuitry block 410 includes any suitable type of processing circuit that includes one or more of any components of the processor circuit 210. Similarly, the CW Doppler processing circuitry block 420 is a processor circuit, a part of a processor circuit, or a part of the processor circuit 210 shown in FIG. 2. The CW Doppler processing circuitry block 420 also includes any suitable type of processing circuit that includes one or more of any components of the processor circuit 210.

[0055]

[0062] FIG. 5A is a schematic diagram showing an exemplary ultrasonic transducer array 512 according to an aspect of the present disclosure. The ultrasonic transducer array 512 includes a plurality of ultrasonic transducers 510 arranged in a sub-array 520.

[0056]

[0063] The transducer array 512 shown in FIG. 5A is an ultrasonic element 510 in a 1.X - dimensional or two - dimensional matrix. The transducer array 512 is substantially similar to the transducer array 112 of FIGS. 1 and / or 3. In other embodiments, the transducer array 512 may also be a one - dimensional linear array, or any other suitable type of array. As already mentioned with respect to the transducer array 112, the transducer array 512 includes any suitable number of transducer elements 510. The transducer elements 510 are arranged within the transducer array 512 in a plurality of sub - arrays 520. In addition, the sub - arrays 520 are referred to as groups or patches, among other suitable terms. Each sub - array 520 includes four transducer elements 510, or any other suitable number of transducer elements 510. For example, the sub - array 520 includes 2, 4, 6, 8, 10, 12, or more transducer elements 510, and any suitable number of transducer elements 510 therebetween. In addition, in some embodiments, each sub - array 520 does not have to include the same number of transducer elements 510 and each can vary according to any suitable arrangement configuration or pattern. Note that the separation between the sub - arrays 520 shown in FIG. 5A does not necessarily indicate a physical separation or isolation within the array 512. For example, each of the transducer elements 510 in the array has the same separation from each adjacent element (regardless of whether this element is part of the same sub - array 520). Rather, the separation shown in FIG. 5A illustrates the grouping of the sub - arrays.

[0057]

[0064] Figure 5B is a schematic diagram showing an exemplary circuitry of the analog beamformer 530 according to an aspect of the present disclosure. The analog beamformer 530 is substantially similar to the analog beamformer 314 of FIG. 3. FIG. 5B provides a more detailed perspective of the analog beamformer 530 implemented within an ultrasonic probe. The analog beamformer 530 includes a plurality of transmit pulsers 532, preamplifiers 534, delay circuits 540, a summing component 550, and conductors 590 that provide power, clock, and / or control signals to any of these components. FIG. 5B further depicts a single subarray 520 that includes a plurality of ultrasonic transducer elements 510. The subarray 520 shown in FIG. 5B is either one of the subarrays 520 shown in FIG. 5A or a different subarray.

[0058]

[0065] The transmit pulsers 532 are substantially similar to the pulsers 318 of FIG. 3. Specifically, the transmit pulsers 532 receive command signals from a host and, in response to these command signals, transmit high voltage pulses to activate the ultrasonic device elements 510 and emit ultrasonic energy that propagates within a patient's biological structure. Accordingly, each ultrasonic element 510 corresponds to and / or communicates with a transmit pulser 532.

[0059]

[0066] FIG. 5B additionally depicts a plurality of preamplifiers 534. The preamplifiers 534 are substantially similar to the preamplifiers 319 of FIG. 3. The preamplifiers 534 amplify the signals received from the ultrasonic elements 510 to improve the quality of the received signals, for example, by reducing the noise floor.

[0060]

[0067] A plurality of delay circuits 540 communicate with a preamplifier 534 within an analog beamformer 530. The delay circuits 540 may be of any suitable type. For example, the delay circuits 540 include analog delay circuits for the analog beamformer 530. The delay circuits 540 apply a delay profile to signals received from the ultrasonic transducer 510 to perform beamforming, or partial beamforming, for all elements within the subarray 520. Such a delay profile is provided to the delay circuits 540 by any suitable method. For example, in some embodiments, conductors corresponding to control data or clock data within the conductor 590 communicate with the delay circuits 540 and specify a delay profile for the delay circuits 540.

[0061]

[0068] FIG. 5B further depicts a summing component 550. The summing component 550 is an analog addition circuit, an addition mixer, or any suitable electronic component for adding signals. The summing component 550 communicates with the individual outputs of the delay circuits 540. In such a configuration, the signals output from each delay circuit 540 are added in an analog manner. Otherwise, in other embodiments, the summing component 550 includes any suitable circuitry or configuration for combining the signals from the outputs of the delay circuits 540. The output of the summing component 550 then communicates with one or more of the T / R switches 316 of FIG. 3, and the signals combined by the analog beamformer 530 are further processed and / or combined within the probe 110 and / or the host 130 in the manner described or any other suitable manner.

[0062]

[0069] FIG. 6 is a flowchart of an ultrasonic imaging method 600 according to an aspect of the present disclosure. As illustrated, method 600 includes several recited steps, although embodiments of method 600 may include additional steps before, after, or in between the recited steps. In some embodiments, one or more of the recited steps may be omitted, performed in a different order, or performed simultaneously. The steps of method 600 are performed by any suitable component within ultrasonic imaging system 100, and not all steps need to be performed within the same component. In some embodiments, one or more steps of method 600 may be performed by, or under the direction of, a processor circuit of ultrasonic imaging system 100, including, for example, processor 260 (FIG. 2) or any other component.

[0063]

[0070] In step 605, method 600 includes generating an analog ultrasonic signal. A command signal is generated at host 130 and transmitted to probe 110 via signal line 392. Pulser 318 then generates a signal to excite the transducer elements of transducer array 112 to generate ultrasonic waves (FIG. 3). Transducer array 112 then also receives echo signals reflected from features in the patient's anatomy and generates an analog electrical signal representative of the ultrasonic echoes. The generated analog ultrasonic signal is then transmitted to circuit network block 310 (FIG. 3).

[0064]

[0071] In step 610, method 600 includes generating an analog continuous wave (CW) Doppler signal within ultrasonic probe 110 using an in-phase / quadrature (I / Q) mixer based on the analog ultrasonic signal. The CW Doppler signal is generated using a plurality of I mixers 382 and Q mixers 384 (FIG. 3). The I mixers 382 and Q mixers 384 may include multiplier mixers or any other suitable type of mixer. Probe 110 includes one or more quadrature clock generators 380 (FIG. 3) that provide additional inputs to I mixers 382 and Q mixers 384 to reduce the analog ultrasonic signal to baseband frequency and create an appropriate phase shift between the output of I mixer 382 and the output of Q mixer 384.

[0065]

[0072] In step 615, method 600 includes transmitting the analog CW Doppler signal to a processor circuit within host 130. The CW Doppler signal is transmitted to host 130 via cable 390, a conductor, a twisted pair, a coaxial cable, a twinaxial cable, or any other suitable signal line within cable 390, or by any suitable method.

[0066]

[0073] In step 620, method 600 includes processing an analog CW Doppler signal. Processing the analog CW Doppler signal includes any suitable data processing component or procedure, including filtering via a low-pass filter, a high-pass filter, or any suitable type of filter. Data processing includes windowing, summing, averaging, smoothing, conversion from one domain to another such as using a Fourier transform, and any other suitable conditioning to improve overall data quality, clarity, or presentation. Signal processing additionally includes converting the analog CW Doppler signal to a digital CW Doppler signal. In such embodiments, signal processing is also performed digitally via software, using hardware such as the physical circuitry within host 130, or by any other suitable method or form, via a standard personal computer and / or processor.

[0067]

[0074] In step 625, method 600 includes generating a graphical representation of blood flow velocity over one or more cardiac cycles. The graphical representation includes any suitable data presentation. For example, the graphical representation includes a simple list of data including data regarding the time, velocity, dimension, or location of an object of interest within the patient's anatomy. The graphical representation additionally includes a Doppler spectrum or other applicable spectrum, plot, or other graphical representation. The graphical representation also includes any suitable plot, picture, or drawing that conveys information related to the patient's health or physical condition to the user. The graphical representation of the blood flow velocity distribution, or other fluid velocity, is output to a display 132 (FIG. 1) that communicates with a processor circuit 134 (FIG. 1) or any other suitable processor described herein.

[0068]

[0075] Those skilled in the art will recognize that the above-described apparatus, system, and method can be modified in various ways. Accordingly, those skilled in the art will understand that the embodiments encompassed by the present disclosure are not limited to the specific exemplary embodiments described above. In this regard, exemplary embodiments are shown and described, but extensive modifications, variations, and substitutions are contemplated in the foregoing disclosure. It should be understood that such variations can be made to the above without departing from the scope of the present disclosure. Accordingly, it should be understood that the appended claims are to be interpreted broadly and in a manner consistent with the present disclosure.

Claims

1. An ultrasonic probe that communicates with an ultrasonic system, the ultrasonic probe comprising: A transducer array that generates analog ultrasonic signals from a plurality of receiving elements; A plurality of analog in-phase / quadrature (I / Q) mixers disposed within the housing of the ultrasonic probe and communicating with the transducer array, each of the plurality of analog I / Q mixers generating an analog continuous wave (CW) Doppler signal based on the analog ultrasonic signal from a corresponding one of the plurality of receiving elements, and the outputs of each of the plurality of analog I / Q mixers being added together; the plurality of analog in-phase / quadrature (I / Q) mixers; A cable coupled to the housing, the cable including a plurality of conductors that transmit the analog CW Doppler signal from the ultrasonic probe to the ultrasonic system; the cable Comprising; The added analog CW Doppler signal includes an added in-phase (I) signal and an added quadrature (Q) signal; The plurality of conductors includes a first conductor that transmits the added I signal and a second conductor that transmits the added Q signal; an ultrasonic probe.

2. An ultrasonic probe that communicates with an ultrasonic system, the ultrasonic probe comprising: A transducer array that generates an analog ultrasonic signal; An analog in-phase / quadrature (I / Q) mixer disposed within the housing of the ultrasonic probe and communicating with the transducer array, the analog I / Q mixer generating an analog continuous wave (CW) Doppler signal based on the analog ultrasonic signal; the analog in-phase / quadrature (I / Q) mixer; A cable coupled to the housing, the cable transmitting the analog CW Doppler signal from the ultrasonic probe to the ultrasonic system; the cable Comprising; Further comprising an analog-to-digital converter (ADC) disposed within the housing and communicating with the transducer array, the ADC converting the analog ultrasonic signal into a digital ultrasonic signal, and the cable transmitting the digital ultrasonic signal to the ultrasonic system; an ultrasonic probe.

3. The ultrasonic probe according to claim 2, further comprising at least one of a digital beamformer or a multiplexer that communicates with the ADC.

4. The ultrasonic probe according to claim 2, wherein the cable includes a first plurality of conductors that transmit the digital ultrasonic signal.

5. The ultrasonic probe according to claim 1, further comprising a quadrature phase clock generator disposed in the housing and communicating with the plurality of analog I / Q mixers.

6. The ultrasonic probe according to claim 5, wherein the cable includes a plurality of conductors that transmit power, a clock, and control signals from the ultrasonic system to the quadrature phase clock generator.

7. The ultrasonic probe according to claim 1, further comprising an analog beamformer disposed in the housing and communicating with the transducer array.

8. An ultrasonic probe according to claim 1, and the ultrasonic system A device comprising: the ultrasonic system is separated from the ultrasonic probe, and the cable extends between the ultrasonic probe and the ultrasonic system.

9. The ultrasonic system includes a processor circuit, and the processor circuit generates a graphical representation of the blood flow velocity distribution based on the analog CW Doppler signal, and outputs the graphical representation to a display communicating with the processor circuit. The device according to claim 8, which performs the above.

10. An ultrasonic probe communicating with an ultrasonic system, the ultrasonic probe comprising: a transducer array that generates an analog ultrasonic signal; and an analog in-phase / quadrature phase (I / Q) mixer disposed in the housing of the ultrasonic probe and communicating with the transducer array, wherein the analog I / Q mixer generates an analog continuous wave (CW) Doppler signal based on the analog ultrasonic signal; and a cable coupled to the housing, the cable transmitting the analog CW Doppler signal from the ultrasonic probe to the ultrasonic system. and the ultrasonic system A device comprising: the ultrasonic system is separated from the ultrasonic probe, the cable extends between the ultrasonic probe and the ultrasonic system, the ultrasonic system includes a processor circuit, and the processor circuit generates a graphical representation of the blood flow velocity distribution based on the analog CW Doppler signal, and outputs the graphical representation to a display communicating with the processor circuit. which performs the above. The ultrasonic probe converts the analog ultrasonic signal into a digital ultrasonic signal, the cable transmits the digital ultrasonic signal from the ultrasonic probe to the ultrasonic system, and the processor circuit generates an ultrasonic image of the heart based on the digital ultrasonic signal, and outputs the ultrasonic image to the display to perform, an apparatus.

11. generating an analog ultrasonic signal from a plurality of receiving elements in a transducer array of an ultrasonic probe; generating an analog continuous wave (CW) Doppler signal based on the analog ultrasonic signal using a plurality of analog in-phase / quadrature (I / Q) mixers disposed within a housing of the ultrasonic probe, wherein each of the plurality of analog I / Q mixers generates the analog CW Doppler signal based on the analog ultrasonic signal from a corresponding one of the plurality of receiving elements; adding individual outputs of the plurality of analog I / Q mixers, wherein the added analog CW Doppler signal includes an added in-phase (I) signal and an added quadrature (Q) signal; transmitting the analog CW Doppler signal from the ultrasonic probe to an ultrasonic system spaced apart from the ultrasonic probe by a cable coupled to the housing, the cable including a first conductor for transmitting the added I signal and a second conductor for transmitting the added Q signal; generating a graphical representation of blood flow velocity based on the analog CW Doppler signal using a processor circuit of the ultrasonic system; outputting the graphical representation to a display in communication with the processor circuit to have, a method.

Images