Ultrasound asynchronous resonance imaging (ARI) technique for needle tip localization

Abstract

The present invention discloses an ultrasonic scanner that can perform a needle tip detection process that includes transmitting a first ultrasonic pulse signal at a first time point. The first ultrasonic pulse signal can be configured to generate a first echo signal by adjacent tissue and the needle within the tissue. The scanner can receive the first echo signal from the needle upon reaching a second time point after a predetermined delay period from the first time point. The scanner can generate needle tip image data corresponding to the location of the needle based on the first echo signal. The scanner can perform a tissue detection process and / or generate a composite image including a visual indicator of the location of the needle tip relative to the tissue based on the needle tip image data and the tissue image data.

Description

[Background technology]

[0001] (CROSS REFERENCE TO RELATED APPLICATIONS) This application claims priority to U.S. Provisional Patent Application No. 63 / 288,072, filed December 10, 2021, U.S. Provisional Patent Application No. 63 / 293,322, filed December 23, 2021, U.S. Provisional Patent Application No. 63 / 296,607, filed January 5, 2022, U.S. Provisional Patent Application No. 63 / 299,558, filed January 14, 2022, U.S. Provisional Patent Application No. 63 / 307,701, filed February 8, 2022, U.S. Provisional Patent Application No. 63 / 318,986, filed March 11, 2022, and U.S. Provisional Patent Application No. 63 / 348,160, filed June 7, 2022, the disclosures of each of which are incorporated herein by reference for all purposes.

[0002] Medical ultrasound techniques may include medical imaging, diagnostic, and / or therapeutic techniques using ultrasound energy. Ultrasound energy can be used to create images of internal body structures such as tendons, muscles, joints, blood vessels, and internal organs. Ultrasound energy can also be used to monitor the pregnancy process. Ultrasound energy can be used to measure / image dynamic medical variables (such as blood flow). Medical ultrasound techniques are also referred to as medical sonography and medical diagnostic ultrasound.

[0003] Ultrasound energy emissions may consist of sound waves (e.g., ultrasound) at frequencies higher than the range of human hearing (e.g., above 20,000 Hz). Ultrasound imaging is performed by directing ultrasound energy (e.g., pulses of ultrasound) at a target tissue using one or more imaging probes. The ultrasound pulses may be reflected by tissue, such as the target tissue, and received by one or more imaging probes. Ultrasound echo energy / pulses / signals may have different reflection characteristics. Medical ultrasound devices use ultrasound echo signals for imaging, diagnostic, or therapeutic processes. Summary of the Invention

[0004] Techniques are disclosed relating to an ultrasound scanner device and / or techniques performed thereby. The ultrasound scanner may include one or more imaging probes. The one or more techniques may include performing a needle tip detection process. The needle tip detection process may include transmitting one or more first ultrasound pulse signals at a first time. The one or more first ultrasound pulse signals may be configured to generate one or more first echo signals by adjacent tissue and / or a needle within the tissue.

[0005] The technique can include receiving one or more first echo signals from the needle upon reaching a second time point that is delayed a predetermined delay period from the first time point. The technique can include generating needle tip image data corresponding to a position of the needle tip based on the one or more first echo signals.

[0006] The technique can include performing a tissue detection process. The tissue detection process can include transmitting one or more second ultrasonic pulse signals. The one or more second ultrasonic pulse signals can be configured to generate one or more second echo signals by adjacent tissue and the needle in the tissue. The technique can include receiving one or more second echo signals from the adjacent tissue. The technique can include generating tissue image data corresponding to the adjacent tissue based on the one or more second echo signals.

[0007] The technique can include generating a composite image. The composite image can include a visual indicator of the position of the needle tip relative to the tissue based on the needle tip image data and / or the tissue image data. The technique can include displaying the composite image on a display.

[0008] Techniques are disclosed relating to one or more ultrasound scanner devices and / or one or more techniques performed thereby. The one or more ultrasound scanner devices may include one or more imaging probes. The one or more ultrasound scanner devices may include a display. The one or more ultrasound scanner devices may include one or more processors. At least one processor may be configured to perform a needle tip detection process. The processor may be configured to transmit one or more first ultrasound pulse signals at a first time point. The one or more first pulse signals may be configured to generate one or more first echo signals by adjacent tissue and / or the needle within the tissue. The processor may be configured to receive one or more first echo signals from the needle upon reaching a second time point delayed by a predetermined delay period from the first time point. The processor may be configured to generate needle tip image data corresponding to a position of the needle tip based on the one or more first echo signals.

[0009] The processor can be configured to perform a tissue detection process. The processor can be configured to transmit one or more second ultrasonic pulse signals. The one or more second ultrasonic pulse signals can be configured to generate one or more second echo signals by adjacent tissue and the needle in the tissue. The processor can be configured to receive one or more second echo signals from the adjacent tissue. The processor can be configured to generate tissue image data corresponding to the adjacent tissue based on the one or more second echo signals.

[0010] The processor can be configured to generate a composite image based on the needle tip image data and the tissue image data, the composite image including a visual indicator of the position of the needle tip relative to the tissue. The processor can be configured to display the composite image on the display. Techniques are disclosed relating to one or more ultrasound scanner devices and / or one or more techniques performed thereby. The ultrasound scanner may have an imaging probe. The one or more techniques may include performing a target object detection process. The target object detection process may include transmitting one or more first ultrasound pulse signals at a first time point. The one or more first ultrasound pulse signals may be configured to generate one or more first echo signals by adjacent tissue and a target object within the tissue. The techniques may include receiving one or more first echo signals from the target object upon reaching a second time point delayed by a predetermined delay period from the first time point. The techniques may include generating target object image data corresponding to a location of the target object based on the one or more first echo signals.

[0011] The technique may include performing a tissue detection process. The tissue detection process may include transmitting one or more second ultrasonic pulse signals. The one or more second ultrasonic pulse signals may be configured to generate one or more second echo signals by adjacent tissue and a target object within the tissue. The technique may include receiving one or more second echo signals from the adjacent tissue. The technique may include generating tissue image data corresponding to the adjacent tissue based on the one or more second echo signals.

[0012] Techniques can include generating a composite image based on the target object image data and the tissue image data, the composite image including a visual indicator of the location of the target object relative to the tissue, and displaying the composite image on a display.

[0013] Techniques are disclosed relating to one or more ultrasound scanner devices and / or one or more techniques performed thereby. The ultrasound scanner may include one or more imaging probes. The one or more techniques may include transmitting one or more ultrasound pulse signals at a first time. The one or more ultrasound pulse signals may be configured to generate one or more echo signals by adjacent tissue and a needle within the tissue.

[0014] The technique can include performing a needle tip detection process. The needle tip detection process can include receiving one or more echo signals from the needle when a second time point is reached that is delayed from the first time point by a predetermined delay period. The technique can include generating needle tip image data corresponding to a position of the needle tip based on the one or more echo signals.

[0015] The technique can include performing a tissue detection process. The tissue detection can include receiving one or more echo signals from adjacent tissue. The technique can include generating tissue image data corresponding to the adjacent tissue based on the one or more echo signals.

[0016] The techniques can include generating a composite image based on the needle tip image data and the tissue image data, the composite image including a visual indicator of the position of the needle tip relative to the tissue. The techniques can include displaying the composite image on a display. [Brief description of the drawings]

[0017] The elements and other features, advantages and disclosures contained herein, and the manner in which they are accomplished, will become apparent and the invention will be better understood by reference to the following description of various embodiments of the invention in conjunction with the accompanying drawings. [Figure 1] FIG. 1 illustrates an example of an M-mode ultrasound technique. [Diagram 2] FIG. 2 is an example of an M-mode tracing showing the movement of the mitral valve leaflets. [Diagram 3] FIG. 3 shows an example display of the A-mode technique, which allows display of echo amplitude as a function of depth. [Figure 4] FIG. 4 is a block diagram of the hardware configuration of an exemplary device capable of controlling one or more of the ultrasound devices described herein. [Diagram 5] Figure 5 shows an example of a B-mode ultrasound image with good visualization of the soft tissue but relatively poor conspicuity / visibility of the needle tip. [Figure 6] FIG. 6 shows an example of a ring-down artifact in an ultrasound image. [Figure 7] FIG. 7 shows a block diagram of an exemplary imaging sequence for the B-mode technique. [Figure 8] FIG. 8 shows a block diagram of an exemplary asynchronous resonance imaging (ARI) technique. [Figure 9] FIG. 9 shows an example of a double ring-down artifact consisting of repeated short horizontal lines. [Figure 10] FIG. 10 shows an example of a double ring-down artifact with a confluent appearance and "searchlight" lines on either side. [Figure 11] FIG. 11 shows an example of a double ring-down artifact with an incompletely visualized lower portion. [Figure 12A] FIG. 12A shows an example of a needle tip image obtained with asynchronous resonant imaging with a time delay of 35 microseconds. [Figure 12B] FIG. 12B shows an example of a needle tip image obtained with asynchronous resonant imaging with a time delay of 40 microseconds. [Figure 12C] FIG. 12C shows an example of a needle tip image obtained with asynchronous resonant imaging with a time delay of 45 microseconds. [Figure 13] FIG. 13 shows an example of the location of the focused pulse, focal region, and needle tip in the center of the image. [Figure 14] Figure 14 shows an example of a plane wave pulse, with the needle tip position at the center of the image. [Figure 15]Figure 15 shows an example of a focused pulse, with the focal region in the center of the image and the needle tip position to the right of the image. [Figure 16] Figure 16 shows an example of a plane wave pulse with the needle tip location on the right side of the image. [Figure 17] FIG. 17 shows a block diagram illustrating an imaging sequence for focused wave pulse asynchronous resonance imaging. [Figure 18] FIG. 18 shows a block diagram illustrating an imaging sequence for plane wave pulse asynchronous resonance imaging. [Figure 19] FIG. 19 shows an example of TGC at a typical level for standard B-mode imaging and at the maximum image level used for asynchronous resonance imaging. [Figure 20] FIG. 20 shows an example of visualization of double ring-down artifacts with TGC and processing gain multiplier of 1 at a typical B-mode level. [Figure 21] FIG. 21 shows an example of the visualization of the double ring-down artifact with TGC maximized at all levels and a processing gain multiplier of 15. [Figure 22] FIG. 22 shows a block diagram of an exemplary asynchronous resonance imaging radio frequency data accumulation and averaging sequence. [Figure 23] FIG. 23 shows an exemplary single image acquisition without accumulation and averaging of radio frequency data, in which the double ring-down artifact at the needle tip may not be properly visualized. [Figure 24] Figure 24 illustrates the accumulation and averaging of radio frequency data from multiple image acquisitions to create a single image frame in which the double ring-down artifact of the needle tip can be adequately visualized. [Diagram 25] FIG. 25 shows an asynchronous resonance image of the double ring-down artifact at the needle tip acquired with a time delay of 80 microseconds. [Figure 26] FIG. 26 shows an asynchronous resonance image of the double ring-down artifact at the needle tip acquired with a time delay of 180 microseconds. [Figure 27]FIG. 27 shows an asynchronous resonance image of the double ring-down artifact at the needle tip acquired with a time delay of 400 microseconds. [Figure 28] FIG. 28 shows an exemplary needle tip asynchronous resonance image acquired with a pulse duration of one cycle. [Figure 29] FIG. 29 shows an exemplary needle tip asynchronous resonance image acquired with a pulse duration of 25 cycles. [Diagram 30] FIG. 30 shows an exemplary needle tip asynchronous resonance image acquired with a pulse duration of 100 cycles. [Diagram 31] FIG. 31 shows a needle tip asynchronous resonance image obtained with a center frequency transmit pulse of 5.00 megahertz. [Diagram 32] FIG. 32 shows a needle tip asynchronous resonance image obtained with a center frequency transmit pulse of 5.43 megahertz. [Diagram 33] FIG. 33 shows a needle tip asynchronous resonance image obtained with a center frequency transmit pulse of 6.58 megahertz. [Figure 34A] FIG. 34A shows an exemplary needle tip asynchronous resonance image where the time delay is too short. [Figure 34B] FIG. 34B shows an asynchronous resonance image using a bandpass filter. [Diagram 35] FIG. 35 shows an example of a B-mode technique image with the needle tip in the center of the image. [Diagram 36] FIG. 36 shows an example of an asynchronous resonance image in which a double ring-down artifact of the needle tip is present. [Figure 37] FIG. 37 shows an example of a composite image in which the location of the needle tip is indicated by the narrowest point of the double ring-down artifact. [Figure 38] FIG. 38 shows a block diagram of an exemplary combined imaging sequence using separate image acquisition strategies. [Figure 39] FIG. 39 shows a block diagram of an exemplary compound imaging sequence using a compound image acquisition strategy. [Diagram 40] FIG. 40 is an example showing the effect of probe slicing on visualization of an inserted needle. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0018] For the purposes of promoting an understanding of the principles of the present disclosure, reference will be made to the examples illustrated in the drawings, and specific descriptive language will be used, however, it will be understood that no limitation to the scope of the disclosure is intended thereby.

[0019] The technology used to produce standard ultrasound images is sometimes referred to as "B-mode" (brightness mode) imaging. This technique allows for the production of two-dimensional images of a subject's / patient's anatomy. At least two other imaging modes may be used in certain clinical areas, but both are one-dimensional techniques.

[0020] Techniques such as "M-mode" (motion mode) can be used in echocardiography to provide detailed information about the movement of the walls and / or valves of a subject's / patient's heart. To generate an M-mode display, the ultrasound scanner device can hold an ultrasound beam in a fixed position and transmit and receive (e.g., repeatedly) along this beam. For example, the display of echoes may be slowly scanned from left to right across the screen over the course of several seconds.

[0021] Structures that are stationary relative to the probe (e.g., the subject / patient's chest wall) may appear at a constant depth and therefore as a horizontal line. Structures that are moving towards or away from the probe (e.g., the heart wall) may move up or down on the screen, so the display records their position as a function of time, as shown in Figure 1. Figure 1 illustrates an example of an M-mode ultrasound technique. In Figure 1, an imaging probe / transmitter 106 can transmit a beam directed along a line of sight, shown by the dashed line. At 110, the resulting M-mode display shows the depth of tissue structures along this line of sight as a function of time, for example over several seconds. The M-mode display can provide information such as the amount of movement, speed of movement, and acceleration of individual structures.

[0022] Figure 1 shows the relative positions of structures and how they change over time (e.g., maximum and / or minimum diameter of the ventricle and / or the movement of the two valve leaflets as the valve opens and closes). Figure 2 is an example of an electrocardiogram (ECG) tracing displayed on an ultrasound image screen, for example to provide a timing reference. Figure 2 is an example of an M-mode tracing showing the movement of the mitral valve leaflets.

[0023] Another one-dimensional imaging mode is the A-mode (e.g., amplitude mode) display. The beam is held in a fixed position and the scanner / machine can transmit and receive along this line of sight. Figure 3 shows an example of an A-mode technique display that can display echo amplitude as a function of depth. A-mode displays / techniques can be useful in certain exams, such as some ophthalmic scans, in part because they allow accurate measurement of the depth of various echoes. Referring again to the two-dimensional medical ultrasound technique, also known as "B-mode," this technique can be used to provide image guidance for needle tip location in needle placement procedures. B-mode ultrasound provides (e.g., excellent) images of soft tissue structures, such as blood vessels. In one or more scenarios, the needle tip may not be properly visualized in B-mode. This creates a situation where the clinician can see the target blood vessel on the ultrasound image, but cannot or may not effectively guide the needle tip to the target. Figure 5 shows an example of a B-mode image with good soft tissue visualization, but poor (e.g., relatively) visibility of the needle tip. The B-mode ultrasound image in Figure 5 is of a pork belly phantom. The needle tip is present near the center of Figure 5, but cannot be easily distinguished from other hyperechoic structures in the image.

[0024] In one or more scenarios, B-mode ultrasound "ring-down" artifacts may appear as vertical lines. The vertical lines may (for example) consist of repeated short horizontal lines that begin at a particular point and progress to the bottom of the image screen. The short horizontal lines may expand laterally as the distance from the original point increases. Figure 6 shows an example of a ring-down artifact in an ultrasound image with an imaging depth of 30 millimeters. In Figure 6, a ring-down artifact can be seen in an ultrasound image of the lungs. This is also called a "B-line" and arises from a lesion at the lung-pleural interface. It can also be produced by metallic objects such as medical devices. Although needles are composed of metal, needle tips (for example, normally) may not produce a ring-down artifact.

[0025] In one or more scenarios, a given feature, such as in a B-mode ultrasound image, among other scenarios, its lateral location can be determined by the relative intensity of echoes received by individual elements on a one-dimensional element array of an ultrasound transducer. Its depth location can be determined by the time that elapses between the transmitter / probe transmitting a pulse and the probe / receiver receiving an echo from that feature / structure / tissue. The relationship between depth location in an image and the time between the transmission of a pulse and the reception of an echo is known in the art as the "pulse-echo principle." In B-mode ultrasound, the echo reception period begins when a pulse is transmitted and is the time that elapses (e.g., may be precisely recorded) between the transmission of the pulse and the reception of one or more echoes, or each echo. This allows an image to be reconstructed with the exact depth of the included features. In standard B-mode ultrasound, the needle tip may produce a ring-down artifact echo that is likely obscured by the more intense echoes from the surrounding soft tissue. For these reasons and others, the needle tip ring-down artifact may not be visualized.

[0026] As described herein, hereafter referred to as asynchronous resonance imaging (ARI), ARI can use a time delay between when an ultrasound pulse is transmitted and when the echo reception period begins. For example, for an image depth of 20 millimeters, a time delay (e.g., typically 40-500 microseconds and / or 100-400 microseconds) can be used. Once the time delay ends, the echo reception period begins. Again by way of example, for an image depth of 20 millimeters, the echo reception period can last approximately 26 microseconds, given that the speed of sound in soft tissue is a constant of 1.54 millimeters per microsecond, and the maximum depth round trip is 40 millimeters.

[0027] In one or more scenarios, adjusting the (eg, pre-determined) delay period may not change the depth of the narrowest portion of the double ring-down artifact displayed by the composite image.

[0028] In one or more scenarios, the longest delay period during which a double ring-down artifact echo at the needle tip may still be present may be in the range of 160-500 microseconds. In one or more scenarios, such as when using very long / strong pulses and / or specialized needles, a double ring-down artifact echo may occur after a longer delay period.

[0029] In one or more scenarios, the shortest delay period where tissue echoes are weak enough to be removed by signal processing or are nonexistent is in the range of 40-200 microseconds. For example, placing a needle tip in a bathtub of water will not produce a tissue echo and may show a ring-down artifact in standard B-mode imaging, but may not show a double ring-down artifact.

[0030] In one or more scenarios, a shorter delay period may result in stronger needle tip and / or tissue echoes. A shorter delay period (e.g., too short) may result in tissue echoes obscuring the needle tip double ring-down artifact. A longer delay period (e.g., too long) may result in weaker or no double ring-down artifact. The optimal delay period that maximizes visibility of the double ring-down artifact may vary depending on machine settings and patient factors. In one or more scenarios, the delay period (e.g., predetermined and user / operator adjustable) may be as short as possible without, for example, causing tissue echoes.

[0031] During the time delay, the soft tissue echo dissipates. In one or more scenarios, a ring-down artifact echo from the needle tip may persist due to resonance generation. A standard B-mode image reconstruction can be performed on the received echoes, assigning the start of the echo reception period to time zero (0), e.g., when the ultrasound pulse is transmitted. A double ring-down artifact at the needle tip may be visualized.

[0032] 7 shows a block diagram of an exemplary imaging sequence / technique 702 for a (e.g., standard) B-mode technique. At 704, at least one pulse may be generated in a target tissue. At 706, one or more echo signals may be received. At 708, reception of the one or more echo signals may be terminated. At 710, an image may be constructed / reconstructed using the received echo signals.

[0033] 8 illustrates an example block diagram of an asynchronous resonance imaging (ARI) technique / sequence 802. At 806, at least one pulse may be generated in a target tissue. At 810, a time delay (e.g., predetermined and / or user adjustable) may be observed before receiving one or more echo pulses / signals. At 814, reception of one or more echo signals may be initiated. At 818, reception of one or more echo signals may be terminated. At 822, at least one image may be constructed / reconstructed using the received echo signals.

[0034] In one or more scenarios, perhaps a typical ring-down artifact may arise from a shape in the image and propagate to the bottom of the image, while in other scenarios, asynchronous resonance imaging may create a double ring-down artifact. In a double ring-down artifact, two ring-down artifacts may arise from the needle tip, one propagating to the bottom of the image and the other to the top of the image. The narrowest point of the ring-down artifact may be at the needle tip. It may widen as it propagates toward the top and / or bottom of the image, creating, for example, an "X" shaped shape (such as the letter "X", an hourglass, etc.). The needle tip may be located at the narrowest point of the double ring-down artifact.

[0035] The term "double ring-down artifact" is a technical term corresponding to the technology described herein. The term "ring-down artifact" is a technical term in the field and refers to a vertical line composed of repeated horizontal lines starting from the object of interest (e.g., a needle tip). The ring-down artifact may propagate to the bottom of the image and / or spread laterally as the depth increases. The double ring-down artifact may include at least two ring-down artifacts originating from the needle tip. One ring-down artifact may propagate to the bottom of the image / screen. Another ring-down artifact may propagate to the top of the image / screen. The upward propagating ring-down artifact may be generated by one or more time delays described herein.

[0036] Although perhaps similar to the ring-down artifact in standard B-mode imaging, the double ring-down artifact may consist of repeated short horizontal lines, appear to merge, or may only be partially visualized. Two side "searchlight" lines with a slope approximately parallel to the edge of the lower ring-down artifact may appear laterally of the double ring-down artifact. The double ring-down artifact is a concept covered by one or more of the technologies and / or techniques described herein.

[0037] Examples of double ring-down artifacts created by asynchronous resonance imaging are shown in Figures 9, 10, and 11. Figure 9 shows an example of a double ring-down artifact composed of short repeating horizontal lines. Figure 10 shows an example of a double ring-down artifact with a merging appearance and "searchlight" lines on either side. Figure 11 shows an example of a double ring-down artifact with incomplete visualization of the bottom.

[0038] In one or more scenarios, the pulse-echo principle may not apply to the double ring-down artifact of asynchronous resonance imaging. This may apply to soft tissue echoes. Regardless of the increase and / or decrease in time delay, the location of the needle tip can be accurately determined by the narrowest point of the double ring-down artifact. For example, an asynchronous resonance image may be acquired with a time delay of 40 microseconds and with the actual physical depth of the needle tip in the image plane being 7 millimeters, producing an image that includes a double ring-down artifact with its narrowest point at a depth of 7 millimeters. Using a soft tissue speed of sound constant of 1.54 millimeters / microsecond, the pulse-echo principle predicts that a reduction or increase in the time delay of 5 microseconds may increase or decrease the depth of the narrowest point of the double ring-down artifact by 3 millimeters, respectively.

[0039] In one or more scenarios, images acquired with, for example, a 35, 40, or 45 microsecond time delay may actually result in the narrowest point of the double ring-down artifact (e.g., may all result in) at a depth of 7 millimeters, which corresponds to the actual physical depth of the needle tip, whereas a 35 microsecond time delay image may result in soft tissue features 6 millimeters deeper compared to a 45 microsecond time delay image. An example is shown in Figures 12A, 12B, and 12C.

[0040] Figures 12A, 12B, and 12C show examples of needle tip images obtained with asynchronous resonance imaging with varying time delays. In Figure 12A, the time delay was 35 microseconds. In Figure 12B, the time delay was 40 microseconds. In Figure 12C, the time delay was 45 microseconds. In Figures 12A, 12B, and 12C, the narrowest point of the double ring-down artifact remains at the same depth, but the soft tissue echoes, which appear as horizontal lines, decrease in depth as the time delay increases.

[0041] There are at least two types of pulses that can be used in asynchronous resonance imaging: focused wave and plane wave. The energy of a focused pulse can be concentrated at a specific depth and lateral location called the focal zone. The energy of a plane wave pulse can be evenly distributed across the lateral dimension of the imaging plane. For a focused pulse with a needle tip in the image plane, the conspicuousness of the double ring-down artifact may be greatest when the needle tip is in the focal zone and / or may decrease as the distance from the needle tip to the focal region increases. For a plane wave pulse, the visibility of the double ring-down artifact may be similar regardless of the location of the needle tip in the image. For example, a focused pulse with a needle tip in the focal zone may produce a double ring-down artifact that is more noticeable than a plane wave pulse, all other settings being equal. Examples of the effect of needle tip location on the conspicuousness of the double ring-down artifact when using focused and plane wave pulses are shown in Figures 13, 14, 15, and 16.

[0042] FIG. 13 shows an example of a focused pulse, focal zone, and needle tip location in the center of the image. FIG. 14 shows an example of a plane wave pulse, with the needle tip location in the center of the image. FIG. 15 shows an example of a focused pulse, with the focal zone in the center of the image and the needle tip location to the right of the image. FIG. 16 shows an example of a plane wave pulse with the needle tip location to the right of the image. The most visible double ring-down artifact may appear in the focused pulse image where the focal zone and needle tip locations are coincident. The least visible double ring-down artifact may appear in the focused pulse image where the focal zone and needle tip locations are separated. The double ring-down artifact may be well visualized in both plane wave images and / or may be less noticeable than the double ring-down artifact in the focused pulse image where the focal zone and needle tip locations are coincident.

[0043] In one or more scenarios, there may be multiple double ring-down artifacts. The double ring-down artifact that may indicate the location of the needle tip may be a "high visibility" artifact and / or the final double ring-down artifact seen as the probe leaves the needle. The term "visibility" is a term used by radiologists to indicate how prominent a particular shape is on an image from surrounding structures. Visibility may be, for example, the ratio of the average grayscale intensity of the structure of interest to the average grayscale intensity of the surrounding pixels.

[0044] A highly visible double ring-down artifact may occur, for example, if (e.g., only if) the needle tip is in the imaging plane. Other positions of the needle may produce weaker double ring-down artifacts. Such artifacts can be distinguished from the highly visible ring-down artifact at the needle tip by moving the imaging probe. Other positions of the needle may produce highly visible double ring-down artifacts. These positions can be moved far enough away from the needle tip to be distinguishable from the double ring-down artifact at the needle tip, for example, by moving the imaging probe.

[0045] To detect the location of the needle tip using focused pulses, in various scenarios, one or more or multiple focused pulse asynchronous resonance imaging acquisitions with varying focal zones may be (e.g., may have to be) performed, such that images are acquired at focal zones close to all possible needle tip locations within the image. The images are then processed, and the image containing the most visible double ring-down artifact is kept, and perhaps one or more other images, or all images, are discarded. In one or more scenarios, a single plane wave pulse asynchronous resonance imaging acquisition may be sufficient to produce a double ring-down artifact at any location of the needle tip within the image.

[0046] FIG. 17 shows a block diagram illustrating an imaging sequence / technique 1702 for focused wave pulse asynchronous resonance imaging. At 1706, at least one focused wave pulse can be generated / transmitted to the target tissue. At 1710, a time delay (e.g., predetermined and / or user adjustable) can be observed before receiving an echo signal / pulse. At 1714, reception of one or more echo pulses / signals can begin. At 1716, one or more of 1706, 1710, and / or 1714 can be repeated one or more times. At 1720, one or more images can be reconstructed based on the received one or more echo signals / pulses. At 1724, one or more images can be selected (e.g., as better / best images) and / or one or more images can be discarded, for example, as less useful. At 1728, one or more images (e.g., composite image and other images) can be displayed.

[0047] FIG. 18 shows a block diagram illustrating an imaging sequence / technique 1802 for plane wave pulse asynchronous resonance imaging. At 1806, at least one plane wave pulse can be generated / transmitted to a target tissue. At 1810, a time delay (e.g., predetermined and / or user adjustable) can be observed before receiving an echo signal / pulse. At 1814, reception of one or more echo pulses / signals can begin. At 1820, one or more of 1806, 1810, and / or 1814 can be repeated one or more times. At 1822, one or more images can be reconstructed based on the received one or more echo signals / pulses. At 1824, one or more images (e.g., composite images and other images) can be represented.

[0048] Perhaps due to the larger number of image acquisitions useful (e.g., required) to create a single image frame in focused pulsed asynchronous resonance imaging, among other scenarios, much higher frame rates can be achieved with plane wave pulsed asynchronous resonance imaging. The higher frame rates of plane wave pulsed asynchronous resonance imaging allow for the use of many acquired images to create a (e.g., single) image frame by radio frequency accumulation and averaging imaging.

[0049] The frame rate of focused pulse asynchronous resonance imaging can be improved by combining one or more pulses with a (e.g., single) echo receive period. In one or more scenarios, the pulse repetition frequency may be limited due to hardware specific to medical imaging ultrasound equipment and / or biological effects concerns for patient safety. The number of pulses combined with a (e.g., single) echo receive period may be limited by the duration between the first and last pulses, since the echo from the first pulse may become weaker as the duration between the first and last pulses increases.

[0050] For a pulse of a given duration, a focused pulse may have a greater biological effect than a plane wave pulse, for example due to the energy of the focused pulse being concentrated in a focal zone. Thus, using a plane wave pulse allows for a longer pulse duration without being limited by subject / patient safety or bioeffects concerns. Since bandwidth is inversely proportional to pulse duration, a longer pulse duration results in a narrower bandwidth, for example allowing the energy of the ultrasound pulse to be more closely distributed around the resonant frequency of the needle.

[0051] In one or more scenarios, the needle tip double ring-down artifact echo in asynchronous resonance imaging may be weak. This weakness may be due to a lower intensity of the needle tip ring-down artifact echo compared to the surrounding soft tissue and / or a weakening of one or all echoes during the time delay. For example, it may be useful (e.g., helpful, required, etc.) to use a higher level of gain in asynchronous resonance imaging compared to standard B-mode imaging. Time gain compensation (TGC) is maximized at one or more levels, or at all levels of the image. In one or more scenarios, a processing gain multiplication factor of 15 may be applied to the pixel intensity data, for example, prior to compression, among other phases of the sequence.

[0052] 19 illustrates an example of a (e.g., typical) level of TGC in standard B-mode imaging and a maximum TGC at one or more or all image levels used in, for example, asynchronous resonance imaging. At 1902, a typical level of TGC in standard B-mode imaging is shown. At 1906, a maximum TGC at one or more or all image levels used in asynchronous resonance imaging is shown.

[0053] Figures 20 and 21 show examples of needle tip asynchronous resonance images obtained with typical B-mode gain settings. A typical TGC level and processing gain multiplier of 1 can be used, which may result in poor visualization of the double ring-down artifact. By appropriately setting the asynchronous resonance imaging gain of the TGC at one or more or all levels, the double ring-down artifact may become more prominent.

[0054] 20 and 21 show examples of needle tip asynchronous resonance images obtained with various gain settings. In FIG. 20, with typical B-mode gain settings, TGC at typical B-mode levels, and a processing gain multiplier of 1, the visualization of the double ring-down artifact may be poor. In FIG. 21, with appropriate asynchronous resonance imaging gain settings, maximum TGC at one or more levels, or at all levels, and a processing gain multiplier of 15, the double ring-down artifact may be (e.g., adequate) visible.

[0055] Possibly, it may be useful to accumulate and / or average the radio frequency data, among other things, by acquiring one or more images, to distinguish weak double ring-down artifact echoes from ambient noise, thereby increasing the visibility of the double ring-down artifact.

[0056] To perform the accumulation and averaging of radio frequency data, pixel intensity data is not reconstructed when echo radio frequency data is acquired. Instead, another image acquisition may be performed and the newly acquired radio frequency data may be summed with the previously acquired radio frequency data. This process may be repeated for a (e.g., predetermined) number of image acquisitions, after which the summed radio frequency data may be averaged, for example. The averaged radio frequency data may be used to reconstruct pixel intensity data and display a (e.g., single) image frame.

[0057] FIG. 22 illustrates a block diagram of an exemplary asynchronous resonance imaging radio frequency data accumulation and averaging sequence / technique 2202. In FIG. 22, radio frequency data from, for example, 10 acquired images is accumulated and averaged to create a (e.g., single) displayed image frame. At 2206, at least one plane wave pulse can be generated / transmitted to the target tissue. At 2210, a time delay (e.g., predetermined and / or user adjustable) can be observed before receiving an echo signal / pulse. At 2214, reception of one or more echo pulses / signals begins. At 2216, one or more of 2206, 2210, and / or 2214 can be repeated one or more times. At 2218, radio frequency data can be accumulated. At 2220, the radio frequency data can be averaged. At 2228, one or more images (e.g., composite and other images) are reconstructed and / or displayed.

[0058] 23 and 24 show examples of asynchronous resonance images acquired with and without accumulation and averaging of radio frequency data, respectively. FIG. 23 shows an example of a single image acquisition without accumulation and averaging of radio frequency data, where the double ring-down artifact at the needle tip may not be properly visualized. FIG. 24 shows an example of accumulation and averaging of radio frequency data from, for example, ten images to create a single image frame, where the double ring-down artifact at the needle tip can be properly visualized.

[0059] Possibly due to the higher frame rate of plane-wave pulse asynchronous resonance imaging, among other scenarios, more acquired images can be used for radio frequency data accumulation and averaging when using plane-wave pulses than when using focused pulses.

[0060] In one or more scenarios, one or more first pulse acquisition events may be performed, possibly before proceeding to a second pulse B-mode image acquisition. Radio frequency data from these first pulse acquisition events may be accumulated and / or averaged to create a (e.g., single) first pulse image with enhanced prominence of the needle tip double ring-down artifact. In the case of a plane wave first pulse image acquisition, one or more acquisition events, or some or all of the radio frequency data from each acquisition event may be included in the averaging process. In the case of a focused pulse image acquisition, radio frequency data may be averaged (e.g., only averaged) from acquisition events that include, for example, the same first pulse focal zone.

[0061] Focused pulsing may require one or more rounds of ARI acquisition followed by image processing to ascertain which image contains the best example of the double ring-down artifact. Such best illustrative image can then be used in combination with the B-mode image. For example, with plane wave techniques where one pulse can cover the entire screen / image, multiple rounds may not be necessary.

[0062] There are more than one scenario, e.g., when there is a first transmit pulse signal and a second transmit pulse signal, the first pulse signal can be a focused pulse. An acquisition event can consist of one or more focused pulses with various focal zones and can be combined with (e.g., a single) echo receive period. Data from one or more acquisition events with different focal zones can also be combined to create one image. A significant portion of an image may consist of pixels that are close to the focal zone. The closer the needle tip is to the focal zone, the more visible the double ring-down artifact may be.

[0063] At least one benefit / advantage of using focused pulses is that more energy can be delivered to the needle tip and / or less energy can be delivered to the surrounding soft tissue, which may result in a stronger echo at the needle tip and / or a weaker echo in the soft tissue, which may result in increased visibility of the needle tip double ring-down artifact.

[0064] In one or more scenarios, a drawback of using a first focused pulse is that it may be useful (e.g., necessary) to acquire needle tip data for the entire image, compared to a single acquisition event of a plane wave pulse. This may reduce the frame rate and shorten the time available for accumulating and / or averaging the radio frequency data of the first pulse and / or B-mode imaging of the second pulse. Combining the data from these one or more acquisition events into the needle tip image may require increased image processing, further reducing the frame rate.

[0065] In one or more scenarios, the low frame rate can be mitigated to some extent by using one or more focus pulses per acquisition event. The number of focus pulses per acquisition can be limited to a low number, such as, for example, five. A high number of pulses per acquisition event can reduce the visibility of the needle tip double ring-down artifact in the focal zone from the previous pulse, for example, due to a longer effective delay period. One or more focus pulses in a given acquisition event may be separated by a short time, such as, for example, 10 microseconds from one focused pulse to the next. One or more factors, such as the number of pulses, transmit voltage, and / or pulse duration, are limited by hardware factors, such as the power supply of a typical medical ultrasound device, among others.

[0066] In one or more scenarios, a drawback of using a focused first pulse is that the duration of the first pulse may be limited by biological effects on the subject / patient's soft tissues because the focused pulse concentrates the ultrasound energy in a small area, which may increase the maximum energy and / or power per area compared to images acquired with, for example, a plane wave first pulse.

[0067] In one or more scenarios, for example, where there is a first transmit pulse signal and a second transmit pulse signal, the first pulse signal can be a plane wave pulse. Because a plane wave pulse distributes the energy of the ultrasound pulse evenly across the lateral dimension of the image, a needle tip at a given depth can produce a double ring-down artifact that is equally visible at one or more lateral locations of the needle tip, or at every lateral location. An acquisition event can consist of one or more plane wave pulses and be combined with a (e.g., single) echo receive period. A (e.g., single) plane wave acquisition event can provide needle tip data for the entire image. If the needle tip is anywhere within the image, a double ring-down artifact can occur.

[0068] At least one advantage of using a plane wave pulse is that a relatively high frame rate can be achieved since the needle tip data for the entire image can be acquired in a (e.g., single) acquisition event using a single first pulse. Such a high frame rate can result in a longer time for the first pulse radio frequency data accumulation and / or averaging acquisition event. This can improve the visibility of the needle tip double ring-down artifact. A second pulse B-mode image acquisition can improve image quality of the soft tissue.

[0069] Since the energy of the first pulse of the plane wave is spread evenly laterally, depending on the dimensions of the beam aperture, the maximum energy per unit area may be smaller for a plane wave pulse than for a focused pulse. For a given pulse duration, the biological effect on the subject / patient may be smaller for a plane wave pulse than for a focused pulse. This allows, for example, for longer pulse durations of the plane wave pulse.

[0070] In one or more scenarios, the visibility of the double ring-down artifact at the needle tip may be affected by the duration of the time delay between the ultrasound transmit pulse and the start of the echo reception period. If the time delay is too short, one or more tissue echoes may occur, obscuring the double ring-down artifact. If the time delay is too long, the double ring-down artifact echo may be (e.g., excessively) attenuated. This may result in the double ring-down artifact not being properly visualized or never being visualized.

[0071] The most prominent double ring-down artifact may be produced by a (e.g., shortest) time delay that (e.g., typically) does not result in visualization of tissue echoes. In one or more scenarios, a longer delay may further improve the visibility of the double ring-down artifact. Useful (e.g., optimal) time delays are typically in the range of 40-500 microseconds and / or 100-400 microseconds. This range may vary depending on factors such as machine settings and soft tissue echogenicity. Figures 25, 26, and 27 show examples of images with time delays that are too short, optimal, and too long.

[0072] 25, 26, and 27 show asynchronous resonance images of the double ring-down artifact of the needle tip acquired with various time delays. FIG. 25 shows an asynchronous resonance image of the double ring-down artifact of the needle tip acquired with a time delay of 80 microseconds. If this time delay is too short, the double ring-down artifact may be obscured by tissue echoes. FIG. 26 shows a double ring-down artifact of the needle tip acquired with a time delay of 180 microseconds. This time delay may be appropriate to ensure that the double ring-down artifact is properly visualized. FIG. 27 shows an asynchronous resonance image of the double ring-down artifact of the needle tip acquired with a time delay of 400 microseconds. If this time delay is too long, the double ring-down artifact may be weakly visualized. In one or more scenarios, the visibility of the needle tip double ring-down artifact may be affected by the duration of the ultrasound transmit pulse. In standard B-mode ultrasound, short transmit pulses (e.g., 1 cycle) are used to optimize axial resolution, among other reasons. The visibility of the needle tip double ring-down artifact in asynchronous resonance imaging may be increased by using a transmit pulse of longer duration, e.g., in the range of 5 to 25 cycles. A longer duration transmit pulse allows for increased energy delivered to the needle tip, possibly without increasing the drive power of the transmit pulse, and may result in a stronger double ring-down artifact echo.

[0073] Transmit pulse driving power may be limited by hardware factors and / or regulatory restrictions, due to concerns about patient safety and bioeffects, among other reasons. Pulse bandwidth may be inversely proportional to pulse duration. Longer transmit pulses result in narrower bandwidth, possibly concentrating the transmit pulse energy around the needle resonance frequency. Too long a pulse duration may reduce the visibility of double ring-down artifacts. Figures 28, 29, and 30 show examples of asynchronous resonance images acquired with varying pulse durations. 28, 29, and 30 show examples of needle tip asynchronous resonance images acquired with different pulse durations. FIG. 28 shows an example of a needle tip asynchronous resonance image acquired with a pulse duration of 1 cycle. This duration is too short, so the double ring-down artifact may not be properly visualized. FIG. 29 shows an example of a needle tip asynchronous resonance image acquired with a pulse duration of 25 cycles. This duration may be appropriate to ensure that the double ring-down artifact is properly visualized. FIG. 30 shows an example of a needle tip asynchronous resonance image acquired with a pulse duration of 100 cycles. This duration is too long, so the double ring-down artifact may not be properly visualized.

[0074] A needle with given characteristics such as gauge, length, and material composition may have a unique resonant frequency. Conceivably, the visibility of the needle tip double ring-down artifact may be maximized, among other scenarios, if the center frequency of the asynchronous resonant imaging transmit pulse matches the resonant frequency of the needle. Figures 31, 32, and 33 show an example of an intravenous catheter needle with a free length 2.56 inch (6.50 centimeter) gauge cannula, triple polished lancet A bevel, polymer hub, and stainless steel hypodermic tubing in which a 20 gauge catheter is placed. This may result in a needle tip double ring-down artifact of maximum intensity with a center frequency of the asynchronous resonant imaging transmit pulse of 5.43 megahertz. The intensity of the generated double ring-down artifact may be reduced when the center frequency of the transmit pulse is between 5.00 megahertz and 6.58 megahertz.

[0075] 31, 32, and 33 show needle tip asynchronous resonance images obtained with different center frequencies of the transmit pulse. A 22-gauge intravenous catheter needle with a 20-gauge catheter inserted may be used to obtain the images. FIG. 31 shows a needle tip asynchronous resonance image obtained with a transmit pulse with a center frequency of 5.00 megahertz. At this center frequency, the double ring-down artifact may not be properly visualized. FIG. 32 shows a needle tip asynchronous resonance image obtained with a center frequency transmit pulse of 5.43 megahertz. At this center frequency, the double ring-down artifact may be properly visualized. FIG. 33 shows a needle tip asynchronous resonance image obtained with a center frequency transmit pulse of 6.58 megahertz. At this center frequency, the double ring-down artifact may not be properly visualized.

[0076] The center frequency of the first pulse can be adjusted to provide the most visible double ring-down artifact, which can occur at approximately 5.4 MHz for a 22 regular wall gauge hypodermic tubing needle with a nominal outer diameter of 0.718 mm and a nominal inner diameter of 0.413 mm. If the center frequency of the first pulse is significantly higher or lower than this value, e.g., below 5.0 MHz or above 5.9 MHz for a 22 regular wall gauge hypodermic tubing needle, reduced visibility and / or no double ring-down artifact may occur.

[0077] The center frequency of the second pulse can be adjusted by the user / operator to produce a better / best soft tissue image. The highest frequency that can produce adequate penetration will produce a better / best soft tissue image. This can be determined by the user / operator for each patient, as is common in B-mode medical ultrasound.

[0078] In one or more scenarios, increasing the first pulse duration may result in increased visibility of the double ring-down artifact. Increasing the first pulse duration (e.g., too long) may result in decreased visibility of the double ring-down artifact. Pulse durations in the range of 1-25 cycles may provide good and sufficient visibility of the double ring-down artifact. The optimal first pulse duration may vary depending on, for example, machine settings and patient factors.

[0079] In one or more scenarios, it may be helpful (e.g., important) for asynchronous resonance imaging to use a time delay sufficient to remove one or more or all tissue echoes so that the double ring-down artifact at the needle tip is not obscured. In one or more scenarios, an alternative strategy may include using a shorter time delay, in which case some tissue echoes may still be present and signal processing may be applied. A band-pass filter may be used to remove the tissue echoes to better visualize the double ring-down artifact. This short time delay may increase the intensity of the double ring-down artifact echo, for example.

[0080] Increasing the time delay from the ultrasound pulse to the beginning of the echo reception period can reduce the intensity of both the tissue echo and the needle tip ring-down artifact echo. In the case of the tissue echo, a more rapid decrease can occur. The double ring-down artifact may be best visualized (e.g., typically) with the shortest time delay at which no tissue echo is received. For example, best visualization may be obtained with a time delay at which the ring-down artifact echo is strongest without competing tissue echoes. For example, when the tissue echo is strong and / or long-lasting, situations may arise in which the ring-down artifact echo is significantly weakened by a time delay sufficient to eliminate one or more or all tissue echoes, among other scenarios. This can result in poor visualization of the double ring-down artifact.

[0081] In such scenarios, among other scenarios, a possible strategy is to use a shorter time delay. This can increase the strength of the ring-down artifact echo. The tissue echo, although weakened, is still present and may partially mask the ring-down artifact echo. Applying a band-pass filter to the echo can remove the tissue echo and improve visualization of the double ring-down artifact. The band-pass filter has (for example, typically) a center frequency 0%-20% higher than the center frequency of the transmit pulse, a -3 dB bandwidth of 10%-30% of the center frequency of the band-pass filter, and a -20 dB stop band of 30%-45% of the center frequency of the band-pass filter. For example, a transmit pulse with a center frequency of 5.4 MHz can be combined with a band-pass filter with a center frequency of 5.9 MHz, a -3 dB bandwidth of 5.47-6.33 MHz, and a -20 dB stop band of 4.86-6.94 MHz.

[0082] FIG 34A shows a needle tip asynchronous resonance image with a transmit pulse center frequency of 5.00 MHz and a time delay that is too short so that the double ring-down artifact may be partially obscured by tissue echoes. FIG 34B shows an asynchronous resonance image with a transmit pulse center frequency of 5.00 MHz and the same time delay used to generate the image of FIG 34A. A band pass filter with a center frequency of 6.00 MHz, a bandwidth of 5.60 to 6.40 MHz at -3 dB, and a stop band cutoff frequency of 5.01 MHz and 6.99 MHz at -20 dB may be applied to generate the image of FIG 34B to remove one or more tissue echoes and / or enhance the visibility of the double ring-down artifact.

[0083] Perhaps to optimize ultrasound needle-tip guidance, and for other reasons, a composite image may be created in which the double ring-down artifact indicates the location of the needle tip in a standard B-mode image. B-mode and asynchronous resonance images may be acquired (e.g., separately). This allows the use of transmit pulse characteristics optimized for the type of image being acquired. The B-mode transmit pulse may be shortened, e.g., to one cycle, to optimize axial resolution. For example, for a 20-millimeter-deep soft-tissue image, a higher center frequency (e.g., 8.9 megahertz) may be used to optimize image resolution. The asynchronous resonance imaging transmit pulse may be longer, e.g., 20 cycles, to maximize visibility of the double ring-down artifact. For example, a lower center frequency (e.g., 5.43 megahertz) may be used to match the needle's resonance frequency.

[0084] In one or more scenarios, for example, a B-mode image and an asynchronous resonance image may be acquired (e.g., separately). These images may also be combined to create a composite image. Figures 35, 36, and 37 show examples of creating a composite image. Figure 35 shows an example of a B-mode technique image where the needle tip is in the center of the image. Figure 36 shows an example of an asynchronous resonance image where a needle tip double ring-down artifact is present. Figure 37 shows an example of a composite image where the location of the needle tip is indicated by the narrowest point of the double ring-down artifact.

[0085] In one or more scenarios, a composite image can be created using separate transmit pulses for dedicated B-mode and asynchronous resonance image acquisition. In one or more scenarios, another strategy can include acquiring both B-mode and asynchronous resonance images using a single transmit pulse. At least one advantage of acquiring both images from the same transmit pulse is improved frame rate, which can be beneficial for focused pulse asynchronous resonance imaging, which may be hindered at lower frame rates.

[0086] A potential drawback of acquiring both B-mode and asynchronous resonance images from the same transmit pulse is that the (e.g., optimal) transmit pulse characteristics for B-mode and asynchronous resonance images may be different. Acquiring both B-mode and asynchronous resonance images with the same transmit pulse may result in non-optimal pulse characteristics being used for one or both image types. FIG. 38 illustrates a block diagram of an example of a combined imaging sequence / technique 3802 using separate image acquisition strategies. At 3804, a B-mode pulse can be generated / transmitted to the target tissue. At 3808, reception of B-mode echo signals can be started. At 3812, reception of B-mode echo signals can be terminated. At 3816, a B-mode image is constructed / reconstructed based on the received B-mode echo signals / pulses. At 3820, an asynchronous resonance imaging (ARI) pulse can be generated / transmitted to the target tissue. At 3824, a time delay (e.g., predetermined and / or user adjustable) can be observed before receiving the ARI echo signals. At 3828, an ARI image echo signal reception period can be started. At 3832, an ARI image can be constructed / reconstructed based on the received ARI echo signals. At 3836, a combined image (e.g., based on the ARI image and the B-mode image) can be processed and displayed.

[0087] FIG. 39 illustrates a block diagram of an example of a combined imaging sequence / technique 3902 using a combined image acquisition strategy. At 3904, a B-mode pulse can be generated / transmitted to a target tissue. At 3908, reception of a B-mode echo signal can be initiated. At 3912, reception of a B-mode echo signal can be terminated. At 3924, a time delay (e.g., predetermined and / or user adjustable) can be observed before receiving an asynchronous resonance imaging (ARI) echo signal. At 3928, an ARI image echo signal reception period can be initiated. At 3932, an ARI image and a B-mode image can be constructed / reconstructed based on the received echo signals. At 3936, a combined image (e.g., based on the ARI image and the B-mode image) can be processed and displayed. In one or more scenarios, an imaging probe / transducer of an ultrasound scanner / scanning device can transmit one or more ultrasound pulses. After pulse generation begins, the transducer does not listen for echoes for a period of time (e.g., due to a predefined or adjustable time delay). After the period of time has elapsed, the transducer can start listening for echoes. The scanning device can perform / initiate an echo / receive period that may correlate with the depth of the image to be reconstructed. The scanning device can reconstruct the echoes to create an image. Perhaps if a needle tip is present, a double ring-down artifact can be seen on the image / display. The scanning device can perform a standard ultrasound scan and / or display a (e.g., composite) image on the display.

[0088] FIG. 4 is a block diagram of an exemplary hardware configuration of an apparatus that can function as a process control device / logic controller for executing any of the ultrasonic scanners described herein and / or any of the ultrasonic scanner processes / techniques disclosed herein. The hardware configuration 400 can be in wired and / or wireless communication and / or internet / cloud communication with any of the ultrasonic scanner systems / apparatuses described herein. The hardware configuration 400 is operable to facilitate delivery of information from an internal server of the apparatus. The hardware configuration 400 can include a processor 410, a memory 420, a storage device 430, and / or an input / output device 440. One or more of the components 410, 420, 430, and 440 can be interconnected using, for example, a system bus 450. The processor 410 can process instructions for execution within the hardware configuration 400. The processor 410 can be a single-threaded processor or a multi-threaded processor. The processor 410 can process instructions stored in the memory 420 and / or the storage device 430.

[0089] The memory 420 can store information within the hardware configuration 400. The memory 420 can be a computer readable medium (CRM), such as a non-transitory CRM. The memory 420 can be a volatile memory unit and / or a non-volatile memory unit.

[0090] The storage device 430 can provide mass storage for the hardware configuration 400. The storage device 430 can be a computer readable medium (CRM), for example, a non-transitory CRM. The storage device 430 can include, for example, a hard disk device, an optical disk device, a flash memory, and / or other mass storage devices. The storage device 430 can also be a device external to the hardware configuration 400.

[0091] The input / output devices 440 may provide input / output operations to the hardware configuration 400. The input / output devices 440 (e.g., transceiver devices) may include one or more of a network interface device (e.g., an Ethernet card), a serial communication device (e.g., an RS-232 port), one or more Universal Serial Bus (USB) interfaces (e.g., a USB 2.0 port), and / or a wireless interface device (e.g., an 802.11 card). The input / output devices may include a driver device configured to send communications to and receive communications from one or more networks. The input / output devices 440 may communicate with at least one display device 484. The display device 484 may display any of the ultrasound-generated images described herein.

[0092] The input / output device 400 can communicate with one or more input / output modules (not shown) that may be local to the hardware configuration 400 and / or remote from the hardware configuration 400. The one or more output modules can provide input / output functionality in digital signal formats, discrete signal formats, TTL formats, analog signal formats, serial communication protocols, Fieldbus protocol communications, and / or other open or proprietary communication protocols, etc.

[0093] The camera module 460 can provide digital video input and output capabilities to the hardware configuration 400. The camera module 460 can communicate with any component of the hardware configuration 400, for example, via the system bus 450. The camera module 460 can capture digital images and / or scan various types of images, such as, for example, Universal Product Code (UPC) codes and Quick Response (QR) codes, among other images described herein. For example, a subject / patient record can be made accessible via a QR code or the like. The camera module 460 can scan a subject / patient record QR code to access the subject / patient's (e.g., medical) record and add (e.g., electronically) one or more of the ultrasound images described herein to the subject / patient's medical record.

[0094] The camera module 460 may include at least one microphone device and / or at least one speaker device (not shown). The camera module 460 may communicate with the hardware configuration 400 via wired and / or wireless communication. In one or more scenarios, the camera module 460 may be external to the hardware configuration 400. In one or more scenarios, the camera module 460 may be internal to the hardware configuration 400.

[0095] The ultrasound scanner 480 may be in wired and / or wireless communication with the hardware configuration 400. The ultrasound scanner 480 may be any one of the ultrasound scanners provided / configured to provide at least ultrasound probing and / or imaging as described herein.

[0096] 40 is an example showing the effect of probe slicing on visualization of an inserted needle. At 4010, a schematic of an imaging probe showing a cross-section of the proximal needle insertion into tissue is shown. At 4020, an ultrasound image of the proximal needle visualized above the vein is shown. One or more techniques described herein can facilitate detection of the needle tip inserted into tissue.

[0097] The subject matter of the present disclosure and components thereof may be implemented by instructions that, when executed, cause one or more processing devices to perform the processes and / or functions described herein. Such instructions may include, for example, interpreted instructions, such as script instructions, such as JavaScript or ECMAScript instructions, executable code, and / or other instructions stored on a computer-readable medium.

[0098] Implementations of the objects described in this specification and / or the accompanying figures and / or the functional operations described may be provided as digital electronic circuitry, computer software, firmware, and / or hardware, including the structures disclosed herein and structural equivalents thereof, and / or one or more combinations thereof. The objects described herein may be implemented as one or more computer program products, e.g., as one or more modules of computer program instructions encoded on a tangible program carrier for execution by and / or for controlling the operation of a data processing apparatus.

[0099] A computer program (also called a program, software, software application, script, code) can be written in any form of programming language, including compiled or interpreted, declarative or procedural languages. It can be deployed in any form, including as a stand-alone program or as modules, components, subroutines, and / or other units suitable for use in a computing environment. A computer program may or may not correspond to a file in a file system. A program can be stored as part of a file that holds other programs and / or data (e.g., one or more scripts stored in a markup language document), in a single file dedicated to the program in question, and / or in several coordinated files (e.g., a file that stores one or more modules, subprograms, or portions of code). A computer program can be deployed to be executed on one computer, or on several computers that are at one site, distributed across several sites, or interconnected by a communications network.

[0100] The processes and / or logic flows described herein and / or in the accompanying figures may be performed by one or more programmable processors executing one or more programs to perform functions by operating on input data and / or generating output, thereby tying the processes to a particular machine (e.g., a machine programmed to perform the processes described herein). The processes and / or logic flows, and apparatus may be performed by or implemented as special purpose logic circuitry, such as FPGAs (field programmable gate arrays) and / or ASICs (application specific integrated circuits).

[0101] Computer readable media suitable for storing computer program instructions and / or data include all types of non-volatile memory, media, and memory devices, including, by way of example, semiconductor memory devices (e.g., EPROM, EEPROM, and / or flash memory devices), magnetic disks (e.g., internal hard disks or removable disks), magneto-optical disks, and / or CD-ROM and DVD-ROM disks. The processor and / or memory may be supplemented by, or incorporated in, special purpose logic circuitry.

[0102] Although this specification and the accompanying drawings contain many details of specific embodiments, these should not be construed as limiting the scope of the invention or the claims, but rather as descriptions of specific features of the described examples. Certain features described in this specification in the context of separate embodiments may also possibly be implemented in combination in one embodiment. Various features described in the context of one embodiment may also be implemented separately in multiple combinations or in any suitable subcombination. Although aspects may be described above as functioning in a particular combination and / or possibly claimed (e.g., initially) as such, one or more aspects of the claimed combination may, in some cases, be deleted from the combination. The claimed combination may be subject to subcombinations and / or subcombination variations.

[0103] Although the figures may depict operations in sequence, this should not be understood as requiring that such operations be performed in the particular order and / or sequential order depicted, and / or that all of the depicted operations be performed, to achieve useful results. The described program components and / or systems are typically packaged in a single software product or multiple software products.

[0104] Examples of the subject matter described herein have been described. The actions recited in the claims can be performed in different order to achieve useful results, unless expressly stated otherwise. For example, the processes depicted in the accompanying figures do not require the particular order shown, or sequential order, to achieve useful results. Multitasking and parallel processing may be advantageous in one or more scenarios.

[0105] While the present disclosure has been shown and described in detail in the drawings and foregoing description, the same are to be considered as illustrative and not restrictive in nature, it being understood that only specific examples have been shown and described, and that all changes and modifications that come within the spirit of the disclosure are protected.

Claims

1. 11. A method performed by an ultrasound scanner, the ultrasound scanner comprising an imaging probe, the method comprising: a) executing a needle tip detection process by the scanner, the needle tip detection process comprising: a-i) transmitting, at a first time, one or more first ultrasonic pulse signals with the imaging probe, the one or more first ultrasonic pulse signals configured to generate one or more first echo signals by adjacent tissue and a needle within the tissue; a-ii) receiving, by the imaging probe, the one or more first echo signals from the needle at a second time point that is a predetermined delay period from the first time point; a-iii) generating needle tip image data corresponding to a position of the needle tip based on the one or more first echo signals by the scanner; performing a needle tip detection process, including: b) performing, with said scanner, a tissue detection process, said tissue detection process comprising: b-i) transmitting one or more second ultrasonic pulse signals via the imaging probe, the one or more second ultrasonic pulse signals configured to generate one or more second echo signals by the adjacent tissue and the needle in the tissue; b-ii) receiving, at the imaging probe, the one or more second echo signals from the adjacent tissue; and b-iii) generating, by the scanner, tissue image data corresponding to the adjacent tissue based on the one or more second echo signals; performing a tissue detection process, comprising: c) generating, with the scanner, a composite image based on the needle tip image data and the tissue image data, the composite image including a visual indicator of the position of the needle tip relative to the tissue; d) displaying, by said scanner, said composite image on a display; The method according to claim 1, further comprising:

2. 2. The method of claim 1, wherein in the tissue detection process, there is no predetermined delay period between the transmission of the second pulse signal and the reception of the one or more second echo signals.

3. 2. The method of claim 1, wherein in the needle tip detection process, the first echo signal is not received between the first time point and the second time point.

4. 2. The method of claim 1, wherein any of steps a) through d) are repeated one or more times to produce a plurality of composite images that together form a video.

5. The visual indicator of the position of the needle tip includes: an upper ring-down artifact propagating from the location of the needle tip toward the top of the composite image; a bottom ring-down artifact propagating from the location of the needle tip toward the bottom of the composite image; 2. The method of claim 1, wherein the double ring-down artifact comprises:

6. 6. The method of claim 5, wherein the narrowest point of the upper ring-down artifact and the narrowest point of the lower ring-down artifact each correspond to the location of the needle tip.

7. 2. The method of claim 1, wherein the predetermined delay period is user adjustable.

8. 2. The method of claim 1, wherein the predetermined delay period is a value in the range of 40 to 500 microseconds.

9. 2. The method of claim 1, wherein the predetermined delay period is a value in the range of 100 to 400 microseconds.

10. the predetermined delay period being relatively short such that the tissue echoes partially mask the double ring-down artifact; 2. The method of claim 1, wherein one or more tissue echoes produced in the composite image are removed using signal processing.

11. 2. The method of claim 1, wherein the needle tip detection process includes applying a greater gain to the received first echo signal than a gain applied to the one or more second echo signals of the tissue detection process.

12. 2. The method of claim 1, wherein the first pulsed signal has a center frequency of about 5.4 MHz and the second pulsed signal has a center frequency of about 8.9 MHz.

13. 2. The method of claim 1, wherein at least one of the center frequency of the first pulse signal or the center frequency of the second pulse signal is user adjustable.

14. The method of claim 1 , wherein the needle does not include a transmitter.

15. In the needle tip detection process, the first pulse signal is a focused pulse signal; 2. The method of claim 1, wherein at least one of steps a-i) or a-ii) is repeated two or more times.

16. 2. The method according to claim 1, wherein in the needle tip detection process, the first pulse signal is a plane wave pulse signal.

17. The method of claim 1 , wherein the imaging probe can include one or more imaging probes.

18. The method of claim 1, wherein the needle tip detection process is repeated one or more times before performing the tissue detection process, the needle tip image radio frequency data is accumulated and averaged, and generation of the composite image is based on the accumulated and averaged needle tip image radio frequency data.

19. An imaging probe; A display and A processor; 1. An ultrasound scanner device comprising: The processor includes at least a) a needle tip detection process, the needle tip detection process further comprising: a-i) transmitting at a first time one or more first ultrasonic pulse signals, the one or more first ultrasonic pulse signals configured to generate one or more first echo signals by adjacent tissue and the needle within the tissue; a-ii) receiving the one or more first echo signals from the needle at a second time point that is a predetermined delay period from the first time point; a-iii) generating needle tip image data corresponding to a position of the needle tip based on the one or more first echo signals; The needle tip detection process is configured to b) a tissue detection process, the tissue detection process further comprising: b-i) transmitting one or more second ultrasonic pulse signals, the one or more second ultrasonic pulse signals configured to generate one or more second echo signals by the adjacent tissue and the needle within the tissue; b-ii) receiving the one or more second echo signals from the adjacent tissue; b-iii) generating tissue image data corresponding to the adjacent tissue based on the one or more second echo signals; Run the organization discovery process, which is configured to c) generating a composite image based on the tip image data and the tissue image data, the composite image including a visual indicator of the position of the tip relative to the tissue; d) displaying the composite image on a display; The present invention is characterized in that the present invention is configured as follows: Ultrasound scanner device.

20. 20. The apparatus of claim 19, wherein the processor is further configured such that during the tissue detection process, there is no predetermined delay period between the transmission of the second pulse signal and the reception of the one or more second echo signals.

21. 20. The apparatus of claim 19, wherein the processor is further configured to, during the needle tip detection process, not receive the first echo signal between the first time point and the second time point.

22. 20. The apparatus of claim 19, wherein the processor is further configured to repeat any of a) through d) one or more times to generate a plurality of composite images that together form a video.

23. The processor further comprises: The visual indicator of the position of the needle tip comprises: an upper ring-down artifact propagating from the location of the needle tip toward the top of the composite image; a bottom ring-down artifact propagating from the location of the needle tip toward the bottom of the composite image; 20. The apparatus of claim 19, configured to result in a double ring-down artifact comprising:

24. 24. The apparatus of claim 23, wherein the narrowest point of the upper ring-down artifact and the narrowest point of the lower ring-down artifact each correspond to the location of the needle tip.

25. 20. The apparatus of claim 19, wherein the processor is further configured such that the predetermined delay period is user adjustable.

26. 20. The apparatus of claim 19, wherein the processor is further configured to cause the predetermined delay period to be at least one of a value in a range of 40 to 500 microseconds or a value in a range of 100 to 400 microseconds.

27. The processor further comprises: determining whether the predetermined delay period is relatively short such that the tissue echo partially masks the double ring-down artifact; 20. The apparatus of claim 19, configured to remove one or more tissue echoes produced in the composite image using signal processing.

28. 20. The apparatus of claim 19, wherein to perform the needle tip detection process, the processor is further configured to impart a greater gain to the received first echo signal than a gain imparted to the one or more second echo signals of the tissue detection process.

29. 20. The apparatus of claim 19, wherein the processor is further configured such that the first pulsed signal has a center frequency of approximately 5.4 MHz and the second pulsed signal has a center frequency of approximately 8.9 MHz.

30. 20. The apparatus of claim 19, wherein the processor is further configured to make at least one of the center frequency of the first pulsed signal or the center frequency of the second pulsed signal adjustable by a user.

31. 20. The device of claim 19, wherein the needle does not include a transmitter.

32. In the needle tip detection process, the processor further comprises: the first pulse signal is a focused pulse signal, 20. The apparatus of claim 19, wherein at least one element of a-i) or a-ii) is configured to be repeated two or more times.

33. 20. The apparatus of claim 19, wherein in the needle tip detection process, the processor is further configured such that the first pulse signal is a plane wave pulse signal.

34. 20. The apparatus of claim 19, wherein the imaging probe can include one or more imaging probes.

35. The apparatus of claim 19, wherein the processor is further configured to: repeat the needle tip detection process one or more times before performing the tissue detection process; accumulate and average the needle tip image radio frequency data; and generate the composite image based on the accumulated and averaged needle tip image radio frequency data.

36. 11. A method performed by an ultrasound scanner, the ultrasound scanner comprising an imaging probe, the method comprising: a) performing, by said scanner, a target object detection process, said target object detection process comprising: a-i) transmitting, at a first time, with the imaging probe, one or more first ultrasonic pulse signals configured to generate one or more first echo signals by adjacent tissue and a target object within the tissue; a-ii) receiving, by the imaging probe, the one or more first echo signals from the target object at a second time point that is a predetermined delay period from the first time point; a-iii) generating, by the scanner, target object image data corresponding to a position of the target object based on the one or more first echo signals; performing a target object detection process, including: b) performing, with said scanner, a tissue detection process, said tissue detection process comprising: b-i) transmitting one or more second ultrasonic pulse signals via the imaging probe, the one or more second ultrasonic pulse signals configured to generate one or more second echo signals by the adjacent tissue and the target object within the tissue; b-ii) receiving, at the imaging probe, the one or more second echo signals from the adjacent tissue; and b-iii) generating, by the scanner, tissue image data corresponding to the adjacent tissue based on the one or more second echo signals; performing a tissue detection process, comprising: c) generating, with the scanner, a composite image based on the target object image data and the tissue image data, the composite image including a visual indicator of the location of the target object relative to the tissue; d) displaying, by said scanner, said composite image on a display; The method according to claim 1, further comprising:

37. 37. The method of claim 36, wherein the target object comprises a metallic material.

38. 11. A method performed by an ultrasound scanner, the ultrasound scanner comprising an imaging probe, the method comprising: a) transmitting, at a first time point, one or more ultrasound pulse signals with the imaging probe, the one or more ultrasound pulse signals configured to generate one or more echo signals by adjacent tissue and a needle within the tissue; b) executing a needle tip detection process by the scanner, the needle tip detection process comprising: b-i) receiving, by the imaging probe, the one or more echo signals from the needle at a second time point that is a predetermined delay period from the first time point; b-ii) generating, by the scanner, needle tip image data corresponding to a position of the needle tip based on the one or more echo signals; performing a needle tip detection process, including: c) performing, with said scanner, a tissue detection process, said tissue detection process comprising: ci) receiving, at the imaging probe, the one or more echo signals from the adjacent tissue; c-ii) generating, with the scanner, tissue image data corresponding to the adjacent tissue based on the one or more echo signals; performing a tissue detection process, comprising: d) generating, with the scanner, a composite image based on the needle tip image data and the tissue image data, the composite image including a visual indicator of the position of the needle tip relative to the tissue; e) displaying, by said scanner, said composite image on a display; The method according to claim 1, further comprising:

39. 40. The method of claim 38, wherein any of steps a) through e) are repeated one or more times to generate a plurality of composite images that together form a video.

40. 39. The method of claim 38, wherein the predetermined delay period is at least one of a value in the range of 40 to 500 microseconds, or a value in the range of 100 to 400 microseconds.

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