Technologies for hypodermic needles with collars

Abstract

A hypodermic needle may be configured for detection in sonographic imaging of tissue. The needle may comprise a needle tube, a hub, and a collar. The needle tube may comprise an outer surface, a proximate end, and a distal end. The distal end may comprise a needle tip. The hub may comprise a hub bore proximate to a center of the hub. The hub may be in fixed connection to the outer surface of the needle tube at least proximate to the hub bore. The collar may comprise a collar bore proximate to a center of the collar. The collar may be in fixed connection to the outer surface of the needle at least proximate to the collar bore. The collar may be configured to decrease damping of a radiated wave propagated by the needle tip in response to sonographic energy excitation into the tissue.

Description

TECHNOLOGIES FOR HYPODERMIC NEEDLES WITH COLLARSCROSS-REFERENCE TO RELATED APPLICATIONS

[0001] The present application claims the benefit of United States Provisional Patent Application No. 63 / 619,062, filed January 9, 2024; United States Provisional Patent Application No. 63 / 621,137, filed January 16, 2024; United States Provisional Patent Application No. 63 / 551,562, filed February 9, 2024; United States Provisional Patent Application No. 63 / 560,319, filed March 1, 2024; United States Provisional Patent Application No. 63 / 678,818, filed August 2, 2024; United States Provisional Patent Application No. 63 / 678,847, filed August 2, 2024; United States Provisional Patent Application No. 63 / 678,854, filed August 2, 2024; and United States Provisional Patent Application No. 63 / 703,152, filed October 3, 2024, the entirety of all of which are incorporated herein by reference, for all purposes.BACKGROUND

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

[0003] Ultrasound energy emissions may be composed of sound waves (e.g., ultrasound waves) with frequencies which are higher than the those in the range of human hearing (e.g., greater than 20,000 Hz). Ultrasonic imaging is conducted by sending ultrasound energy (e.g., pulses thereof) into target tissue using one or more imaging probes. The ultrasound pulses may echo off of tissues, such as the target tissues, and may be received by the one or more imaging probes. The ultrasound echo energy / pulses / signals may have different reflection properties. Medical ultrasound devices may use the ultrasound echo signals for the imaging, diagnostic, or therapeutic processes.BRIEF SUMMARY

[0004] An asynchronous resonance image of the tip of a hypodermic needle in tissue may include a visual indicator of the position of the needle tip. For example, the visual indicator may be aringdown artifact. Visualization of the visual indicator may be improved, perhaps for example if the hypodermic needle includes a metal part joined to the needle tube of the hypodermic needle. The shape of the metal part may be configured to discourage / impede that metal part being gripped by the user / operator of the needle, as visualization of the visual indicator may be worsened due to damping effect of such a contact / grip / touch.

[0005] A hypodermic needle may include at least two parts joined / connected to a needle tube. One part may be a hub, which may have a shape and / or construction / structure configured to encourage / facilitate a grip / touch / contact by the user / operator of the needle. Another part may be a collar that maybe composed of a metal. The collar may have a shape and / or construed on / structure that may discourage / impede a grip of the user / operator of the needle. In an asynchronous resonance image of the tip of the hypodermic needle in tissue, visualization of a visual indicator of the position of the needle tip may be improved because of the metal collar. Because of the metal composition of the collar and / or as an operator grip / contact of the collar is discouraged / impeded, worsened visualization of the visual indicator may be avoided.

[0006] In one or more scenarios, a hypodermic needle may be configured for detection in sonographic imaging of tissue. The needle may comprise a needle tube. The needle tube may comprise an outer surface, a proximal end, and a distal end. The distal end may comprise a needle tip. The needle may comprise a hub. The hub may comprise a hub bore proximate to a center of the hub. The hub may be in fixed connection to the outer surface of the needle tube at least proximate to the hub bore. The needle may comprise a collar. The collar may comprise a collar bore proximate to a center of the collar. The collar may be in fixed connection to the outer surface of the needle at least proximate to the collar bore. The collar may be configured to decrease damping of a radiated wave propagated by the needle tip in response to sonographic energy excitation transmitted into the tissue.

[0007] In one or more scenarios, a sonographic system may be configured for imaging in tissue. The system may comprise an ultrasound scanner. The ultrasound scanner may comprise a display device and / or a processor. The processor may be configured to transmit sonographic energy into the tissue. The processor may be configured to process a time-delayed based image of the tissue. The processor may be configured to process a non-time delayed image of the tissue. The processor may be configured to generate a compound image of the tissue based on the time-delayed based image of the tissue and the non-time delayed based image of the tissue. The processor may beconfigured to render the compound image of the tissue on the display device. The system may comprise a hypodermic needle configured for insertion into the tissue.

[0008] The needle may comprise a needle tube. The needle tube may comprise an outer surface, a proximal end, and / or a distal end. The distal end may comprise a needle tip. The needle may comprise a hub. The hub may comprise a hub bore proximate to a center of the hub. The hub may be in fixed connection to the outer surface of the needle tube at least proximate to the hub bore. The needle may comprise a collar. The collar may comprise a collar bore proximate to a center of the collar. The collar may be in fixed connection to the outer surface of the needle at least proximate to the collar bore. The collar may be configured to decrease damping of a radiated wave propagated by the needle tip in response to the sonographic energy excitation transmitted into the tissue. The compound image may include at least one visual indicator of the needle tip. The decrease damping may cause an improvement in visualization of the visual indicator relative to a visual indicator corresponding to a hypodermic needle configured without a collar.

[0009] In one or more scenarios, a method for imaging in tissue may be processed. The method may comprise transmitting, by an ultrasound scanner, sonographic energy into the tissue. The method may comprise processing, by the ultrasound scanner, a time-delayed based image of the tissue. The method may comprise processing, by the ultrasound scanner, a non-time delayed image of the tissue. The method may comprise generating, by the ultrasound scanner, a compound image of the tissue based on the time-delayed based image of the tissue and the non-time delayed based image of the tissue. The method may comprise rendering, by the ultrasound system, the compound image of the tissue on a display device. The compound image may comprise a visual indicator of a needle tip of a hypodermic needle inserted into the tissue.

[0010] The hypodermic needle may comprise a needle tube. The needle tube may comprise an outer surface, a proximal end, and / or a distal end. The distal end may comprise the needle tip. The needle may comprise a hub. The hub may comprise a hub bore proximate to a center of the hub. The hub may be in fixed connection to the outer surface of the needle tube at least proximate to the hub bore. The needle may comprise a collar. The collar may comprise a collar bore proximate to a center of the collar. The collar may be in fixed connection to the outer surface of the needle at least proximate to the collar bore. The collar may decreasing damping of a radiated wave propagated by the needle tip in response to the sonographic energy excitation transmitted into the tissue. The decreasing damping may cause an improvement in visualization of the visual indicator relative to a visual indicator corresponding to a hypodermic needle configured without acollar.BRIEF DESCRIPTION OF THE DRAWINGS

[0011] The present disclosure will become more fully understood from the detailed description and the accompanying drawings, wherein:

[0012] FIG. 1 illustrates an example diagram of a B-mode imaging sequence.

[0013] FIG. 2 illustrates an example block diagram of an asynchronous resonance imaging sequence.

[0014] FIG. 3 A and FIG. 3B illustrate an example response to a pulse from a transducer impacting a point source.

[0015] FIG. 4 is a block diagram of a hardware configuration of an example device that may control one or more elements / devices / processes using a hypodermic needle with a collar.

[0016] FIG. 5A and FIG. 5B are examples of radiofrequency data from imaging a point source.

[0017] FIG. 6A, FIG. 6B, FIG. 6C, and FIG. 6D illustrate delay and sum digital beamforming.

[0018] FIG. 7A, FIG, 7B, FIG. 7C, and FIG. 7D illustrate an example of acoustic radiator signal reconstructed to a ringdown artifact.

[0019] FIG. 8A, FIG. 8B, FIG. 8C, and FIG. 8D illustrate an example effect of the duration of the time delay between the start of pulse transmission and the start of the receive period on a ringdown artifact reaching the top of an image.

[0020] FIG. 9A, FIG. 9B, FIG. 9C, and FIG. 9D illustrate an example effect a time delay between the start of pulse transmission and the start of the receive period on the depth of a tissue object in B-mode imaging.

[0021] FIG. 10A, FIG. 10B, FIG. 10C, FIG. 10D, FIG. 10E, and FIG. 10F illustrate an example wavefront radius effect on depth calculation(s) in ringdown artifacts.

[0022] FIG. 11 A, FIG. 11B, FIG. 11C, and FIG. 11D illustrate an example effect of the duration of the time delay between the start of pulse transmission and the start of the receive period in asynchronous resonance imaging on the depth of the narrowest part of a ringdown artifact.

[0023] FIG. 12A, FIG. 12B, FIG. 12C, FIG. 12D, and FIG. 12E illustrate an example of a compound image acquisition of a needle tip in tissue.

[0024] FIG. 13 illustrates an example isometric view of a needle tube.

[0025] FIG. 14 illustrates an example isometric view of a hypodermic needle that includes a hub joined to a needle tube.

[0026] FIG. 15 illustrates an example of a top view and a section view of a hypodermic needle that includes a hub joined to a needle tube.

[0027] FIG. 16 illustrates an example of an isometric view of a collar joined to a needle tube.

[0028] FIG. 17 illustrates an example top view and a section view of a collar joined to a needle tube.

[0029] FIG. 18A, FIG. 18B, and FIG. 18C illustrate an example of asynchronous resonance image acquisition of the tip of a hypodermic needle in tissue with decreased damping.

[0030] FIG. 19A, FIG. 19B, and FIG. 19C illustrate example asynchronous resonance image acquisition of the tip of a hypodermic needle in tissue with increased damping.

[0031] FIG. 20 illustrates an example isometric view of a hypodermic needle that includes a hub and a collar joined to a needle tube.

[0032] FIG. 21 illustrates an example side view of a hypodermic needle that includes a hub and a collar joined to a needle tube.

[0033] FIG. 22 illustrates an example side view and section view of a hypodermic needle that includes a hub and a collar joined to a needle tube.

[0034] FIG. 23 illustrates an example disc shaped collar with a bore connecting two flat faces.

[0035] The drawings represent one or more aspects of the disclosure and do not limit the scope of invention.DETAILED DESCRIPTION

[0036] The following description of the preferred embodiment(s) is merely exemplary in nature and is in no way intended to limit the invention or inventions. The description of illustrative embodiments is intended to be read in connection with the accompanying drawings, which are to be considered part of the entire written description. In the description of the exemplary embodiments disclosed herein, any reference to direction or orientation is merely intended for convenience of description and is not intended in any way to limit the scope of the present inventions. Relative terms such as “lower,” “upper,” “horizontal,” “vertical,” “above,” “below,” “up,” “down,” “left,” “right,” “top,” “bottom,” “front” and “rear” as well as derivatives thereof (e.g., “horizontally,” “downwardly,” “upwardly,” etc.) should be construed to refer to the orientation as then described or as shown in the drawing under discussion. These relative terms are for convenience of description only and do not require a particular orientation unless explicitly indicated as such. Terms such as “attached,” “affixed,” “connected,” “coupled,” “interconnected,”“secured” and other similar terms refer to a relationship wherein structures are secured or attached to one another either directly or indirectly through intervening structures, as well as both movable or rigid attachments or relationships, unless expressly described otherwise. The discussion herein describes and illustrates some possible non-limiting combinations of features that may exist alone or in other combinations of features. Furthermore, as used herein, the term “or” is to be interpreted as a logical operator that results in true whenever one or more of its operands are true. Furthermore, as used herein, the phrase “based on” is to be interpreted as meaning “based at least in part on,” and therefore is not limited to the interpretation “based entirely on.”

[0037] As used throughout, ranges are used as shorthand for describing each and every value that is within the range. Any value within the range can be selected as the terminus of the range. In addition, all references cited herein are hereby incorporated by reference in their entireties. In the event of a conflict in a definition in the present disclosure and that of a cited reference, the present disclosure controls.

[0038] FIG. 1 illustrates an example diagram 102 of a B-mode imaging sequence. For example, a pulse transmission and the receive period start at (e.g., substantially) the same time.

[0039] FIG. 2 illustrates an example block diagram 202 of an asynchronous resonance imaging sequence. A time delay may be present between the start of pulse transmission and the start of the receive period.

[0040] FIG. 3 A and FIG. 3B illustrate an example response to a pulse from a transducer impacting a point source. In FIG. 3A, an echo 303 from a scatterer 304 propagates toward a transducer 306. In FIG. 3B wavefronts of a continuous wave 308 radiated by an acoustic radiator 310 propagate toward a transducer 312.

[0041] FIG. 5A and FIG. 5B are examples of radiofrequency data from imaging a point source. In the matrices containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. FIG. 5A illustrates a radiofrequency data set from an image acquisition of a scatterer (not shown). The group of letters “X” is a signature created by an echo (not shown) from the scatterer. FIG. 5B illustrates a radiofrequency data set from an image acquisition of an acoustic radiator (not shown). The groups of letters “X” are signatures created by wavefronts (not shown) in a continuous wave radiated by the acoustic radiator. The signatures make up an acoustic radiator signal. Some or all signatures in the acoustic radiator signal may have the same shape.

[0042] FIG. 6A, FIG. 6B, FIG. 6C, and FIG. 6D illustrate delay and sum digital beamforming. In the matrices containing radiofrequency data, time value increases from the top of the matrix to thebottom of the matrix. In the ultrasound images, depth increases from the top of the image to the bottom of the image. FIG. 6A illustrates a radiofrequency data set. The group of letters “X” is a signature. The dashed line is a sampling curve. FIG. 6B illustrates an image reconstructed from the radiofrequency data set in FIG. 6A. A point is visualized in FIG. 6B.

[0043] FIG. 6C illustrates a radiofrequency data set. The group of letters “X” is a signature. The dashed line is a sampling curve. FIG. 6D illustrates an image reconstructed from the radiofrequency data set in FIG. 6C. A curved band is visualized in FIG. 6D.

[0044] In FIG. 6A, the shape of the sampling curve matches the shape of the signature, resulting in visualization of a point in FIG. 6B. In FIG. 6C, the sampling curve is flatter than the signature, resulting in visualization of a concave up curved band in FIG. 6D.

[0045] FIG. 7A, FIG, 7B, FIG. 7C, and FIG. 7D illustrate an example of acoustic radiator signal reconstructed to a ringdown artifact. In the matrices containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. In the ultrasound images, depth increases from the top of the image to the bottom of the image. FIG. 7A and FIG. 7B illustrate B- mode image acquisition of an acoustic radiator (now shown). A pulse transmission (not shown) and the receive period may start at (e.g., substantially) the same time. FIG. 7A illustrates a radiofrequency data set from the acquisition. The groups of letters “X” are signatures in an acoustic radiator signal created by the acoustic radiator (not shown). The dashed lines are sampling curves. FIG. 7B illustrates an image reconstructed from the radiofrequency data set from FIG. 7A. A ringdown artifact, corresponding to the acoustic radiator signal in FIG. 7A, is visualized in FIG. 7B.

[0046] FIG. 7C and FIG. 7D illustrate asynchronous resonance image acquisition of an acoustic radiator (not shown). There may be a time delay between the start of a pulse transmission (not shown) and the start of the receive period. FIG. 7C illustrates a radiofrequency data set from the acquisition. The groups of letters “X” are signatures in an acoustic radiator signal created by the acoustic radiator. The dashed lines are sampling curves. FIG. 7D illustrates an image reconstructed from the radiofrequency data set in FIG. 7C. A ringdown artifact, corresponding to the acoustic radiator signal in FIG. 7C, is visualized in FIG. 7D.

[0047] In FIG. 7A and FIG. 7C, the signature shape is constant, while the sampling curve shape becomes flatter as radiofrequency data time value increases. In FIG. 7A, the acoustic radiator signal is present starting at the radiofrequency data time value equivalent to the depth of the acoustic radiator, where the sampling curve shape matches signature shape, that may correspondto the narrowest part of the ringdown artifact in FIG. 7B. At greater radiofrequency data time values, there may be an increasing mismatch between sampling curve shape and signature shape, resulting in increasing width of the ringdown artifact in FIG. 7B as it advances toward the bottom of the image.

[0048] In FIG. 7C, the acoustic radiator signal is present starting at a radiofrequency data time value less than the equivalent to the depth of the acoustic radiator (not shown). The sampling curve shape matches the signature shape at the radiofrequency data time value equivalent to the depth of the acoustic radiator, that may correspond to the narrowest part of the ringdown artifact in FIG. 7D. At lesser and greater radiofrequency data time values, there may be an increasing mismatch between sampling curve shape and signature shape, resulting in increasing width of the ringdown artifact in FIG. 7D as it advances toward the top and bottom of the image.

[0049] FIG. 8A, FIG. 8B, FIG. 8C, and FIG. 8D illustrate an example effect of the duration of the time delay between the start of pulse transmission (not shown) and the start of the receive period on a ringdown artifact reaching the top of an image. In the matrices containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. In the ultrasound images, depth increases from the top of the image to the bottom of the image.

[0050] FIG. 8A and FIG. 8B illustrate asynchronous resonance image acquisition of an acoustic radiator (not shown) using a time delay that is less than the round trip time between the transducer (not shown) and the acoustic radiator. FIG. 8A illustrates a radiofrequency data set from an acquisition. The groups of letters “X” are signatures in an acoustic radiator signal created by the acoustic radiator. The acoustic radiator signal is not present at the start of the time value range of the radiofrequency data set. FIG. 8B illustrates an image reconstructed from the radiofrequency data set in FIG. 8 A. A ringdown artifact is present in FIG. 8B. The ringdown artifact reaches the bottom of the image. The ringdown artifact does not reach the top of the image.

[0051] FIG. 8C and FIG. 8D illustrate asynchronous resonance image acquisition of an acoustic radiator using a time delay that is greater than the round-trip time between the transducer (not shown) and the acoustic radiator (not shown). FIG. 8C illustrates a radiofrequency data set from an acquisition. The groups of letters “X” are signatures in an acoustic radiator signal created by the acoustic radiator. The acoustic radiator signal is present from the start and continues to the end of the time value range of the radiofrequency data set. FIG. 8D illustrates an image reconstructed from the radiofrequency data set in FIG. 8C. A ringdown artifact is present. The ringdown artifact reaches the top and the bottom of the image.

[0052] FIG. 9 A, FIG. 9B, FIG. 9C, and FIG. 9D illustrate an example effect a time delay between the start of pulse transmission and the start of the receive period on the depth of a tissue object in B-mode imaging. In the matrices containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. In the ultrasound images, depth increases from the top of the image to the bottom of the image.

[0053] FIG. 9A and FIG. 9B illustrate B-mode image acquisition of a tissue object (not shown), with pulse transmission (not shown) and the receive period starting at the same time. FIG. 9A illustrates a radiofrequency data set from an acquisition. The group of letters X is a signal created by echoes from the tissue object. FIG. 9B illustrates an image reconstructed from the radiofrequency data set in FIG. 9A. The tissue object, represented by the circle, is visualized in FIG. 9B.

[0054] FIG. 9C and FIG. 9D illustrate an image acquisition of the tissue object, with a time delay between the start of pulse transmission and the start of the receive period.

[0055] FIG. 9C illustrates a radiofrequency data set from an acquisition. The group of letters X is a signal created by echoes from the tissue object. FIG. 9D illustrates an image reconstructed from the radiofrequency data set in FIG. 9C. The tissue object, represented by the circle, is visualized in FIG. 9D.

[0056] In FIG. 9A, due to pulse transmission and the receive period starting at (e.g., substantially) the same time, the radiofrequency data time value of the signal may match the round trip time between the transducer and the tissue object (not shown). As a result, the depth of the tissue object in the image in FIG. 9B may match the true depth of the tissue object, for example.

[0057] In FIG. 9C, due to the time delay between the start of pulse transmission and the start of the receive period, the radiofrequency data time value of the signal is less than the round trip time between the transducer and the tissue object. As a result, the depth of the tissue object in the image in FIG. 9D is less than the true depth of the tissue object.

[0058] FIG. 10 A, FIG. 10B, FIG. 10C, FIG. 10D, FIG. 10E, and FIG. 10F illustrate an example wavefront radius effect on depth calculation(s) in ringdown artifacts. In the matrices containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. In the ultrasound images, depth increases from the top of the image to the bottom of the image.

[0059] FIG. 10A, FIG. 10B, and FIG. 10C illustrate an asynchronous resonance image acquisition of an acoustic radiator 1004 at a (e.g., relatively) smaller depth. FIG. 10A illustrates one or more wavefronts 1006 of a continuous wave radiated by the acoustic radiator 1004 propagate toward atransducer 1008. FIG. 10B illustrates a radiofrequency data set containing an acoustic radiator signal created by the continuous wave in FIG. 10A. FIG. 10C illustrates an image reconstructed from the radiofrequency data set in FIG. 10B. A ringdown artifact is visualized in FIG. 10C.

[0060] FIG. 10D, FIG. 10E, and FIG. 10F illustrate an asynchronous resonance image acquisition of an acoustic radiator 1012 at a (e.g., relatively) greater depth. FIG. 10D illustrates one or more wavefronts 1014 of a continuous wave radiated by the acoustic radiator 1012 propagating toward a transducer 1016. FIG. 10E illustrates a radiofrequency data set containing an acoustic radiator signal created by the continuous wave in FIG. 10D. FIG. 10F illustrates an image reconstructed from the radiofrequency data set in FIG. 10E. A ringdown artifact is visualized in FIG. 10F.

[0061] In FIG. 10A, FIG. 10B, and FIG. 10C, the (e.g., relatively) smaller depth of the acoustic radiator 1004 results in a decreased radius wavefront received by the transducer 1008 in FIG. 10A, resulting in a decreased flatness signature in the acoustic radiator signal in FIG. 10B. The decreased flatness signature matches the shape of the sampling curve at a smaller radiofrequency data time value, resulting in decreased depth of the narrowest part of the ringdown artifact in FIG.IOC.

[0062] In FIG. 10D, FIG. 10E, and FIG. 10F, the (e.g., relatively) greater depth of the acoustic radiator 1012 results in an increased radius wavefront received by the transducer 1016 in FIG.IOD, resulting in an increased flatness signature in the acoustic radiator signal in FIG. 10E. The increased flatness signature matches the shape of the sampling curve at a larger radiofrequency data time value, resulting in increased depth of the narrowest part of the ringdown artifact in FIG. 10F.

[0063] FIG. 11A, FIG. 11B, FIG. 11C, and FIG. 11D illustrate an example effect of the duration of the time delay between the start of pulse transmission (not shown) and the start of the receive period in asynchronous resonance imaging on the depth of the narrowest part of a ringdown artifact. In the matrices containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. In the ultrasound images, depth increases from the top of the image to the bottom of the image.

[0064] FIG. 11 A and FIG. 1 IB illustrate asynchronous resonance image acquisition of an acoustic radiator using a time delay that is smaller than the time delay used in FIG. 11C and FIG. 1 ID.

[0065] FIG. HA illustrates a radiofrequency data set from an acquisition. The groups of letters are signatures in an acoustic radiator signal created by the acoustic radiator (not shown). FIG. 1 IBillustrates an image reconstructed from the radiofrequency data set in FIG. 11 A. A ringdown artifact is visualized in FIG. 1 IB.

[0066] FIG. 11C and FIG. 1 ID illustrate asynchronous resonance image acquisition of an acoustic radiator (not shown) using a time delay that is larger than the time delay used in FIG. 11A and FIG. 1 IB. The position of the acoustic radiator (not shown) in the imaging plane of the transducer (not shown) is the same as in FIG. 11 A and FIG. 1 IB.

[0067] FIG. 11C illustrates a radiofrequency data set from the acquisition. The groups of letters are signatures in an acoustic radiator signal created by the acoustic radiator. FIG. 1 ID illustrates an image reconstructed from the radiofrequency data set in FIG. 11C. A ringdown artifact is visualized in FIG. 1 ID.

[0068] In FIG. 11C, due to the larger time delay, individual signatures are shifted to smaller radiofrequency data time values. For example, the signature comprised of the letters “b” is in the middle of the matrix in FIG. 11 A, and is at the top of the matrix in FIG. 11C.

[0069] Despite different radiofrequency data time values for individual signatures in FIG. HA and FIG. 11C, the depth of the narrowest part of the ringdown artifact is the same in both images in FIG. 1 IB and FIG. 1 ID. This is because the acoustic radiator is at the same depth in both image acquisitions, such that the radius of the wavefront creating the acoustic radiator signal is the same in both image acquisitions. As a result, the shape of the signature making up the acoustic radiator signal is the same in both image acquisitions of FIG. 1 IB and FIG. 1 ID.

[0070] FIG. 12A, FIG. 12B, FIG. 12C, FIG. 12D, and FIG. 12E illustrate an example of a compound image acquisition of a needle tip in tissue (not shown). A B-mode image is acquired, an asynchronous resonance image is separately acquired, and the B-mode image and the asynchronous resonance image are combined, creating a compound image.

[0071] In the matrices containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. In the ultrasound images, depth increases from the top of the image to the bottom of the image.

[0072] FIG. 12A illustrates a radiofrequency data set from the B-mode image acquisition. The letters “S” are signals created by tissue echoes. FIG. 12C illustrates a radiofrequency data set from the asynchronous resonance image acquisition. The groups of letters “X” are signatures in an acoustic radiator signal created by the needle tip.

[0073] FIG. 12B illustrates a B-mode image reconstructed from the radiofrequency data set in FIG. 12A. Tissue is visualized in FIG. 12B. A ringdown artifact is not visualized in FIG. 12B.

[0074] FIG. 12D illustrates asynchronous resonance image reconstructed from the radiofrequency data set in FIG. 12C. A ringdown artifact is visualized in FIG. 12D. Tissue is not visualized in FIG. 12D.

[0075] FIG. 12E illustrates a compound image created by combining the image in FIG. 12B and the image in FIG. 12D. Both tissue and the ringdown artifact are visualized in FIG. 12E. The narrowest part of the ringdown artifact indicates the position of the needle tip (not shown).

[0076] In the B-mode image acquisition, the continuous wave radiated by the needle tip is not recorded in the radiofrequency data set in FIG. 12A, because it is obscured by stronger echoes from tissue, which create the signals represented by the letters “S”.

[0077] In the asynchronous resonance image acquisition, tissue echoes dissipate during the time delay between the start of pulse transmission and the start of the receive period, while needle tip continuous wave radiation persists, resulting in recording of the continuous wave as an acoustic radiator signal in the radiofrequency data set in FIG. 12C.

[0078] FIG. 13 illustrates an example isometric view of a needle tube 1302. The proximal end 1304 of the needle tube 1302 is blunt. The distal end 1306 of the needle tube 1302 has a sharp point 1308.

[0079] FIG. 14 illustrates an example isometric view of a hypodermic needle 1402 that includes a hub 1404 joined to a needle tube 1406. The distal end 1408 of the needle tube 1406, which has a sharp point 1410, serves as the tip of the hypodermic needle 1402.

[0080] FIG. 15 illustrates an example of a top view 1504 and a section view 1506 of a hypodermic needle 1502 that includes a hub 1508 joined to a needle tube 1510. The top view 1504 of the hypodermic needle 1502 that includes the hub 1508 joined to a needle tube 1510. The dashed line between arrows A-A is a cutting plane line. Section A-A view 1506 illustrates that the needle tube 1510 is inserted into a bore 1512 of the hub 1508, such that the needle tube 1510 and the bore 1512 of the hub 1508 serve as a shaft and hole pairing. A joint is formed between the outer surface of the needle tube 1510 and the surface of the bore 1512 of the hub 1508. The bore 1512 of the hub 1508 extends beyond a proximal end 1514 of the needle tube 1510.

[0081] FIG. 16 illustrates an example of an isometric view 1602 of a collar 1604 joined to a needle tube 1606. The needle tube 1606 is inserted into the bore (not shown) of the collar 1604, such that the needle tube 1606 and the bore of the collar 1604 serve as a shaft and hole pairing. Both ends of the needle tube 1606 extend beyond the bore of the collar 1604. A joint (not shown) is createdbetween the surface (not shown) of the bore of the collar 1604 and the outer surface of the needle tube 1606.

[0082] FIG. 17 illustrates an example top view 1704 and a section view 1706 of a collar 1708 joined to a needle tube 1710 of hypodermic needle 1702. Top view 1704 illustrates a collar 1708 joined to a needle tube 1710. The dashed line between arrows A-A is a cutting plane line. Section view 1706 illustrates a cross section of the needle tube joined to the collar 1708.

[0083] The needle tube 1710 may be inserted into the bore (not shown) of the collar 1708, such that the needle tube 1710 and the bore of the collar 1708 serve as a shaft and hole pairing. Both ends of the needle tube 1710 may extend beyond the bore of the collar 1708. A joint (not shown) may be created between the surface of the bore of the collar 1708 and the outer surface of the needle tube 1710.

[0084] FIG. 18A, FIG. 18B, and FIG. 18C illustrate an example of asynchronous resonance image acquisition of the tip of a hypodermic needle (not shown) in tissue (not shown) with decreased damping. In the matrix containing radiofrequency data, time value increases from the top of the matrix to the bottom of the matrix. In the ultrasound image, depth increases from the top of the image to the bottom of the image.

[0085] In FIG. 18A, one or more wavefronts 1804 of a continuous wave radiated by the needle tip 1806 propagate toward a transducer 1808. The increased thickness of the curved lines indicates increased strength of the continuous wave, which is due to decreased damping in the hypodermic needle (not shown).

[0086] FIG. 18B illustrates a radiofrequency data set corresponding to FIG. 18A. The groups of letters “X” are signatures in an acoustic radiator signal created by the continuous wave in FIG. 18 A. The increased size of the letters “X” indicates increased strength of the acoustic radiator signal, which may be due to the increased strength of the continuous wave.

[0087] FIG. 18C illustrates an image reconstructed from the radiofrequency data set in FIG. 18B. Visualization of a ringdown artifact may be improved due to the increased strength of the acoustic radiator signal in FIG. 18B, resulting in a (e.g., relatively) well visualized ringdown artifact in FIG. 18C.

[0088] FIG. 19A, FIG. 19B, and FIG. 19C illustrate example asynchronous resonance image acquisition of the tip of a hypodermic needle (not shown) in tissue (not shown) with increased damping. In the matrix containing radiofrequency data, time value increases from the top of thematrix to the bottom of the matrix. In the ultrasound image, depth increases from the top of the image to the bottom of the image.

[0089] FIG. 19A illustrates that one or more wavefronts 1904 of a continuous wave radiated by the needle tip 1906 propagate toward a transducer 1908. The decreased thickness of the curved lines indicates decreased strength of the continuous wave, which may be due to increased damping in the hypodermic needle.

[0090] FIG. 19B illustrates a radiofrequency data set corresponding to FIG. 19A. The groups of letters “X” are signatures in an acoustic radiator signal created by the continuous wave in FIG. 19A. The decreased size of the letters “X” indicates decreased strength of the acoustic radiator signal, which may be due to the decreased strength of the continuous wave.

[0091] FIG. 19C illustrates an image reconstructed from the radiofrequency data set in FIG. 19B. Visualization of a ringdown artifact is worsened due to the decreased strength of the acoustic radiator signal in FIG. 19B, resulting in a poorly visualized ringdown artifact in FIG. 19C.

[0092] FIG. 20 illustrates an example isometric view of a hypodermic needle 2002 that includes a hub 2004 and a collar 2006 joined to a needle tube 2010. The surface of the bore (not shown) of the hub 2004 may be joined to the outer surface of the needle tube 2010. The surface of the bore of the collar 2006 may be joined to the outer surface of the needle tube 2010. The bore of the hub 2004 may extend beyond the proximal end (not shown) of the needle tube 2010. Both ends of the needle tube 2010 may extend beyond the bore of the collar 2006.

[0093] FIG. 21 illustrates an example side view of a hypodermic needle 2102 that includes a hub 2104 and a collar 2106 joined to a needle tube 2110. The surface of the bore (not shown) of the hub 2104 may be joined to the outer surface of the needle tube 2110. The surface of the bore of the collar 2106 may be joined to the outer surface of the needle tube 2110. The bore of the hub 2104 may extend beyond the proximal end of the needle tube 2110. Both ends of the needle tube 2110 may extend beyond the bore of the collar 2106. Dimension A is the length of the needle tube 2110 from the hub 2104 to the collar 2106. Dimension B is the length of the needle tube 2110 from the needle tip 2114 to the collar 2106.

[0094] FIG. 22 illustrates an example side view 2204 and section view 2206 of a hypodermic needle 2202 that includes a hub 2208 and a collar 2212 joined to a needle tube 2210. The dashed line between arrows A-A is a cutting plane line. Section view 2206 illustrates a cross section of the collar 2212.

[0095] The surface of the bore (not shown) of the hub 2208 may be joined to the outer surface of the needle tube 2210. The surface of the bore 2218 of the collar 2212 may be joined to the outer surface of the needle tube 2210. The bore of the hub 2208 extends beyond the proximal end (not shown) of the needle tube 2210. Both ends of the needle tube 2210 may extend beyond the bore 2218 of the collar 2212. The bore 2218 of the collar 2212 may have a cylindrical shape, among other shapes not shown. The outer surface of the needle tube 2210 may have a cylindrical shape, among other shapes not shown.

[0096] FIG. 23 illustrates an example disc shaped collar 2302 with a bore 2304 connecting two flat faces 2306 and 2308. FIG. 23 illustrates an isometric view 2310 of the disc shaped collar 2302. FIG. 23 illustrates side view 2312 of the disc shaped collar 2302. Dimension A is the length between the two flat faces 2306 and 2308.

[0097] In view of FIG. 1 to FIG. 23, in medical ultrasound imaging, a pulse may be sent from a transducer. During a receive period, echoes generated by the pulse may be received by the transducer and / or recorded as radiofrequency data. The radiofrequency data may be used to reconstruct an image.

[0098] Radiofrequency data time value zero may correspond to the start of the receive period, such that the start of the receive period may correspond to an image depth zero. In B-mode imaging, pulse transmission and the receive period start at (e.g., substantially) the same time, such that the start of pulse transmission corresponds to image depth zero. In asynchronous resonance imaging, for example as described in World Intellectual Property Organization international publication number WO 2023 / 107745, there may be a time delay between the start of pulse transmission and the start of the receive period, such that a time after the start of pulse transmission may correspond to image depth zero. For example, see FIG. 1 and FIG. 2

[0099] A scatterer may be a point source. An acoustic radiator may be a point source. When a pulse from a transducer impacts a scatterer, a single, discrete echo may be created. When a pulse from a transducer impacts an acoustic radiator, the acoustic radiator may absorb energy from the pulse, and may release the energy over time by radiating a continuous wave, for example. The continuous wave may be considered to be a type of echo.

[0100] An echo from a scatterer and a wavefront in a continuous wave radiated by an acoustic radiator may be point source wavefronts. A wavefront propagating from a point source may be a sphere with a radius equal to the distance from the point source to the wavefront. The intersection of a point source wavefront propagating toward a transducer with the imaging plane of thetransducer may be a circular arc. The radius of a point source wavefront when it is received by a transducer may be (e.g., substantially) equal to the depth of the point source. For example, see FIG. 3 A and FIG. 3B.

[0101] An ultrasound transducer with a one dimensional array of elements, such as a linear array, may be used to record a radiofrequency data set which may be used to create a two dimensional ultrasound image. The radiofrequency data set may be stored in a matrix, with rows corresponding to time from the start of the receive period, and / or columns corresponding to transducer element lateral position, and / or an individual entry having a value corresponding to the strength of a received ultrasound wave.

[0102] When a point source wavefront is received by a transducer, it may create a curve shaped signature in a radiofrequency data set. For example, the shape of the signature may be a branch of a hyperbola. An echo from a scatterer creates a single signature. Wavefronts in a continuous wave radiated by an acoustic radiator can create repeated signatures, which may be referred to as an acoustic radiator signal.

[0103] The radius of a point source wavefront when it is received by a transducer may determine the shape of the corresponding signature. A deeper point source may create a larger radius wavefront, which creates a flatter signature. For a continuous wave radiated by an acoustic radiator, one or more, or each, wavefront received by the transducer has the same radius, which may be equal to the depth of the acoustic radiator. Some or all signatures in an acoustic radiator signal created by the continuous wave may have the same shape. See for example FIG. 5A and FIG. 5B.

[0104] Delay and sum digital beamforming may be used to reconstruct radiofrequency data to pixel data. In delay and sum digital beamforming, a sampling curve may select radiofrequency data, which may be summed to determine the intensity of a pixel. A sampling curve shape for a given radiofrequency data time value may be calibrated to match the predicted shape of a signature created by a point source with an equivalent depth, such that a flatter sampling curve may be used for a greater radiofrequency data time value. If the shape of a sampling curve matches the shape of a signature, a point may be visualized. If the shapes do not match, a curved band may be visualized. As the mismatch increases, the width of the curved band may increase. The curved band is concave down perhaps for example if the signature is flatter than the sampling curve, and concave up perhaps for example if the sampling curve is flatter than the signature. See for example, FIG. 6A, FIG. 6B, FIG. 6C, and FIG. 6D.

[0105] A radiofrequency data set may be acquired in an image acquisition of an acoustic radiator. The radiofrequency data set may contain an acoustic radiator signal created by a continuous wave radiated by the acoustic radiator. Because signature shape in the acoustic radiator signal may be constant, and sampling curve shape may change with radiofrequency data time value to match predicted signature shape, a sampling curve shape may match signature shape at the radiofrequency data time value equivalent to the depth of the acoustic radiator. This may result in a visualization of a point. At other radiofrequency data time values, the changing sampling curve shape does not match the constant signature shape, resulting in visualization of a curved band. As the difference between the radiofrequency data time value of a signature in the acoustic radiator signal and the radiofrequency data time value equivalent to the depth of the acoustic radiator increases, the mismatch between sampling curve shape and signature shape increases. This may result in visualization of a wider curved band. Reconstruction of the radiofrequency data set may visualize a ringdown artifact which may be narrowest at the depth of the acoustic radiator and increases in width as it advances from the depth of the acoustic radiator.

[0106] If pulse transmission and the receive period start at the same time, as in B-mode imaging, the acoustic radiator signal may be present at radiofrequency data time values equal to and greater than the equivalent of the depth of the acoustic radiator. This may result in visualization of a ringdown artifact which may increase in width as it advances from its narrowest part, at the depth of the acoustic radiator, toward the bottom of the image. If there is a time delay between the start of pulse transmission and the start of the receive period, as in asynchronous resonance imaging, the acoustic radiator signal may be present at radiofrequency data time values less than, equal to, and greater than the equivalent of the depth of the acoustic radiator. This may result in visualization of a ringdown artifact which increases in width as it advances from its narrowest part, at the depth of the acoustic radiator, toward the top and bottom of the image. Therefore, in an asynchronous resonance image of an acoustic radiator, the narrowest part of the ringdown artifact created by the acoustic radiator may indicate the position of the acoustic radiator. See for example, FIG. 7A, FIG. 7B, FIG. 7C, and FIG. 7D.

[0107] In an asynchronous resonance image acquisition of an acoustic radiator, if the time delay between the start of pulse transmission and the start of the receive period is less than the round trip time between the transducer and the acoustic radiator, the continuous wave radiated by the acoustic radiator might not reach the transducer before the start of the receive period, such that the acoustic radiator signal created by the continuous wave might not be present at the start of the time valuerange of the acquired radiofrequency data set. Therefore, the corresponding ringdown artifact may reach the bottom of the image, but might not reach the top of the image. If the time delay is greater than the round trip time between the transducer and the acoustic radiator, the continuous wave radiated by the acoustic radiator may reach the transducer before the start of the receive period, such that the acoustic radiator signal may be present from the start and continue to the end of the time value range of the acquired radiofrequency data set, such that the corresponding ringdown artifact may reach the top and the bottom of the image. See for example, FIG. 8A, FIG. 8B, FIG. 8C, and FIG. 8D.

[0108] In B-mode imaging, the time from when a pulse is sent from the transducer to when an echo is received by the transducer is multiplied by a tissue speed of sound constant, such as 1.54 millimeters per microsecond, and multiplied by 0.5 to account for round trip, to determine the depth corresponding to the echo: depth = round trip time * speed of sound constant * 0.5

[0109] Using the time from when a pulse is sent to when a signal is received to determine distance, such as how depth corresponding to an echo is determined in B-mode imaging, is known as time of flight. In B-mode imaging, in order to obtain accurate time of flight calculations, pulse transmission and the receive period begin at the same time, such that the start of pulse transmission corresponds to image depth zero. If a time delay is added between the start of pulse transmission and the start of the receive period, echoes can be shifted to smaller radiofrequency data time values, such that a tissue object in an image may have a depth that is less than the true depth of the tissue object. See, for example, FIG. 9 A, FIG. 9B, FIG. 9C, and FIG. 9D.

[0110] In asynchronous resonance imaging of an acoustic radiator, a continuous wave radiated by the acoustic radiator creates an acoustic radiator signal, which is used to create a ringdown artifact, with the narrowest part of the ringdown artifact accurately indicating the position of the acoustic radiator. Due to the time delay between the start of pulse transmission and the start of the receive period, wavefronts in the continuous wave received at a time after pulse transmission greater than the time-of-flight equivalent of the depth of the acoustic radiator may be used to create the narrowest part of the ringdown artifact. Therefore, the depth of the narrowest part of the ringdown artifact might not be governed by time of flight. Instead, the depth of the narrowest part of the ringdown artifact may be governed by the shape of the signatures making up the acousticradiator signal, which may be governed by the radius of the wavefront in the continuous wave when it may be received by the transducer, which is governed by the depth of the acoustic radiator. The duration of the time delay between the start of pulse transmission and the start of the receive period might not affect wavefront radius, so changing the duration of the time delay might not affect the depth of the narrowest part of the ringdown artifact. See, for example, FIG. 10A to FIG. 10F and FIG. 11A to FIG. 1 ID.

[0111] In an ultrasound image acquisition of the tip of a hypodermic needle, the needle tip may act as an acoustic radiator. For example, in an image acquisition of the tip of a hypodermic needle in short axis orientation relative to the imaging plane of a linear transducer, the needle tip may act as a point source. When a pulse from the transducer impacts the needle tip, the needle tip may absorb energy from the pulse, and may release the energy over time by radiating a continuous wave.

[0112] In aB-mode image acquisition of an acoustic radiator, such as a needle tip, in tissue, such as soft tissue, the continuous wave radiated by the acoustic radiator may be obscured by stronger echoes from tissue. In the B-mode image, tissue may be visualized, and / or a ringdown artifact created by the acoustic radiator might not be visualized.

[0113] In an asynchronous resonance image acquisition of an acoustic radiator, such as a needle tip, in tissue, such as soft tissue, tissue echoes may dissipate during the time delay between the start of pulse transmission and the start of the receive period, such that tissue might not be visualized in the asynchronous resonance image. Continuous wave radiation by the acoustic radiator may persist during the time delay, such that an acoustic radiator signal may be created by the continuous wave. Reconstruction of the acoustic radiator signal may create a visual indicator of the position of the acoustic radiator in the asynchronous resonance image. For example, the visual indicator may be a ringdown artifact, with the narrowest part of the ringdown artifact indicating the position of the acoustic radiator.

[0114] A compound image of an acoustic radiator, such as a needle tip, in tissue, such as soft tissue, can be created by combining a B-mode image and a separately acquired asynchronous resonance image. The B-mode image visualizes tissue. The asynchronous resonance image visualizes a visual indicator of the position of the acoustic radiator. For example, the visual indicator may be a ringdown artifact, with the narrowest part of the ringdown artifact indicating the position of the acoustic radiator. The compound image visualizes both tissue and the visualindicator, such that the position of the acoustic radiator relative to the tissue may be visualized. See, for example, FIG. 12A to FIG. 12E.

[0115] In an asynchronous resonance image acquisition of an acoustic radiator, such as a needle tip, in tissue, the duration of the time delay between the start of pulse transmission and the start of the receive period may affect the acoustic radiator signal created by the acoustic radiator. If the time delay is too short, tissue echoes will remain during the receive period, such that tissue echo signals will obscure the acoustic radiator signal. If the time delay is too long, the continuous wave radiated by the acoustic radiator will dissipate, resulting in a weak acoustic radiator signal. A time delay that works well is long enough for tissue echoes to dissipate, and short enough that the continuous wave radiated by the acoustic radiator persists. This may result in a recording of an adequate acoustic radiator signal created by the continuous wave.

[0116] In an asynchronous resonance image acquisition of an acoustic radiator, such as a needle tip, in tissue, a time delay long enough to allow sufficient decrease in strength of tissue echoes may be typically longer than the round trip time between the transducer and the acoustic radiator, such that the continuous wave radiated by the acoustic radiator reaches the transducer before the start of the receive period.

[0117] In an asynchronous resonance image acquisition of an acoustic radiator, such as a needle tip, in tissue, a plane wave pulse may be used. An advantage of using a plane wave pulse is that a plane wave pulse delivers energy evenly across the lateral dimension of the imaging plane, such that a single plane wave pulse may be used to image an acoustic radiator at any position in the imaging plane, thus allowing a higher frame rate.

[0118] In an asynchronous resonance image acquisition of an acoustic radiator, such as a needle tip, in tissue, the continuous wave radiated by the acoustic radiator during the receive period may be weak. This may result in a weak acoustic radiator signal created by the continuous wave. It may be useful to use an increased pulse duration to improve the strength of the continuous wave. It may be useful to use signal averaging and / or increased gain to improve the strength of the acoustic radiator signal.

[0119] In an asynchronous resonance image acquisition of an acoustic radiator, such as a needle tip, in tissue, a pulse with a center frequency that matches a resonant frequency of the acoustic radiator may result in increased strength of the continuous wave radiated by the acoustic radiator.

[0120] For an asynchronous resonance image acquisition of an acoustic radiator, such as a needle tip, in tissue, settings that may work well may include plane wave pulse, time gain compensationat maximum at all image levels, pixel data multiplied by a processing gain factor in the range of 1 to 250, pulse duration in the range of 1 to 100 cycles, signal averaging performed by averaging radiofrequency data from a number of individual acquisitions in the range of 2 to 50, pulse center frequency in the range of 5.0 to 6.0 megahertz, and time delay between the start of pulse transmission and the start of the receive period greater than or equal to 40 microseconds. A time delay between the start of pulse transmission and the start of the receive period in the range of 40 to 5000 microseconds may work well. Settings outside of these ranges or values may also work well.

[0121] A hypodermic needle may include a hub joined to a needle tube. The proximal end of the needle tube may be blunt. The distal end of the needle tube may have a sharp point. The distal end of the needle tube may serve as the tip of the hypodermic needle. The point facilitates insertion of the needle tube into tissue. See, for example, FIG. 13 and FIG. 14.

[0122] A hypodermic needle may include a hub joined to a needle tube. The hub may have a bore. The needle tube may be inserted into the bore of the hub, such that the needle tube and the bore of the hub may serve as a shaft and hole pairing. A joint may be formed between the outer surface of the needle tube and the surface of the bore of the hub. The bore of the hub may extend beyond the proximal end of the needle tube.

[0123] In a hypodermic needle including a hub joined to a needle tube, the hub may facilitate movement of material, such as liquid, gas, or a guidewire, into and out of the hypodermic needle.

[0124] In a hypodermic needle including a hub joined to a needle tube, the hub may be composed of polymer, such as plastic. A hub composed of polymer, such as plastic, may be less expensive, easier to fabricate, and / or easier to join to the needle tube as compared to a hub composed of other materials. See, for example, FIG. 15.

[0125] A collar may have a bore. A needle tube may be inserted into the bore of the collar, such that the needle tube and the bore of the collar may serve as a shaft and hole pairing. Both ends of the needle tube may extend beyond the bore of the collar. A joint may be created between the surface of the bore of the collar and the outer surface of the needle tube. See, for example, FIG. 16 and FIG. 17.

[0126] An asynchronous resonance image may be acquired of the tip of a hypodermic needle in tissue. Decreased damping of ultrasound waves in the hypodermic needle may result in increased strength of a continuous wave radiated by the needle tip. This may result in increased strength of an acoustic radiator signal created by the continuous wave. This may result in improvedvisualization of a visual indicator of the position of the needle tip, such as a ringdown artifact. See, for example, FIG. 18A to FIG. 18C.

[0127] An asynchronous resonance image may be acquired of the tip of a hypodermic needle in tissue. Increased damping of ultrasound waves in the hypodermic needle may result in decreased strength of a continuous wave radiated by the needle tip. This may result in decreased strength of an acoustic radiator signal created by the continuous wave. This may result in worsened visualization of a visual indicator of the position of the needle tip, such as a ringdown artifact. See, for example, FIG. 19A to FIG. 19C.

[0128] In asynchronous resonance imaging of the tip of a hypodermic needle in tissue, a visual indicator of the position of the needle tip, such as a ringdown artifact, may be visualized. Visualization of the visual indicator may be improved if the hypodermic needle includes a metal part joined to the needle tube of the hypodermic needle. This may be because the metal part may cause decreased damping. However, if the metal part is gripped by a user / operator, visualization of the visual indicator may be worsened due to increased damping caused by gripping the metal part.

[0129] A hypodermic needle may include a hub and a collar joined to a needle tube. The hub may have a bore. The needle tube may be inserted into the bore of the hub, such that the needle tube and the bore of the hub may serve as a shaft and hole pairing. A joint may be formed between the outer surface of the needle tube and the surface of the bore of the hub. The bore of the hub may extend beyond the proximal end of the needle tube. The collar may have a bore. The needle tube may be inserted into the bore of the collar, such that the needle tube and the bore of the collar may serve as a shaft and hole pairing. A joint may be formed between the outer surface of the needle tube and the surface of the bore of the collar. Both ends of the needle tube may extend beyond the bore of the collar. See for example, FIG. 20 and FIG. 21.

[0130] A hypodermic needle may include a hub and a collar joined to a needle tube, as shown in FIG. 20 and FIG. 21. The collar may be composed of metal, such as brass, among other suitable metals. The user / operator may grip the hub. The user / operator does not grip the collar. An asynchronous resonance image of the tip of the hypodermic needle in tissue may visualize a visual indicator of the position of the needle tip, such as a ringdown artifact. Visualization of the visual indicator may be improved because the collar is a metal part joined to the needle tube, which may cause decreased damping. Visualization of the visual indicator may be improved due to decreased damping caused by not gripping the collar.

[0131] If the length of the needle tube from the hub to the collar is too large, the collar may obstruct the view of the user. If the length of the needle tube from the hub to the collar is too large, the collar may limit the insertion of the needle tube into the tissue. For example, a length of the needle tube from the hub to the collar between 0 and 1 millimeters, or between 0 and 2 millimeters, or between 0 and 3 millimeters, or between 0 and 4 millimeters, or between 0 and 5 millimeters, or between 0 and 10 millimeters may work well, among other dimensions.

[0132] If the length of the needle tube from the needle tip to the collar is too small, it may be difficult to reach tissue structures with the needle tip using ultrasound guidance. For example, a length of the needle tube from the needle tip to the collar between 45 and 300 millimeters, or between 50 and 300 millimeters, or between 60 and 300 millimeters may work well, among other dimensions.

[0133] If the outer diameter of the needle tube is too large, it may cause too much tissue trauma. If the outer diameter of the needle tube is too small, it may cause too much bending of the needle tube. For example, an outer diameter of the needle tube in the range of 0.642 millimeters to 1.473 millimeters may work well, among other dimensions.

[0134] There may be a joint between the surface of the bore of the collar and the outer surface of the needle tube. Visualization of the visual indicator may be affected by the shape of the bore of the collar and the shape of the needle tube. A cylindrical shape of the bore of the collar, combined with a cylindrical shape of the outer surface of the needle tube, may result in decreased damping, which may cause improved visualization of the visual indicator. See, for example, FIG. 22.

[0135] Visualization of the visual indicator may be affected by the type of joint between the surface of the bore of the collar and the outer surface of the needle tube. A friction joint, in which friction between the surface of the bore of the collar and the outer surface of the needle tube creates a joint between the surface of the bore of the collar and the outer surface of the needle tube, may result in decreased damping. This may cause improved visualization of the visual indicator. For example, the friction joint may be an interference fit joint, in which a joint is created by an interference fit between the needle tube and the bore of the collar. This may cause decreased damping, resulting in improved visualization of the visual indicator. For example, the friction joint may be a staked joint, in which a joint between the surface of the bore of the collar and the outer surface of the needle tube may be created by staking. This may cause decreased damping, resulting in improved visualization of the visual indicator.

[0136] There may be a friction joint, such as an interference fit joint or a staked joint, between the surface of the bore of the collar and the outer surface of the needle tube. Visualization of the visual indicator may be affected by the type of friction joint between the surface of the bore of the collar and the outer surface of the needle tube. A friction joint that rigidly fixes the position of the collar relative to the needle tube may result in decreased damping, which may cause improved visualization of the visual indicator. For example, a rigidly fixed friction joint may prevent movement of the collar relative to the needle tube with typical manual force.

[0137] There may be a joint, such as a rigidly fixed friction joint, between the surface of the bore of the collar and the outer surface of the needle tube. If the collar, including the surface of the bore of the collar, has a metal coating, damping may be decreased, resulting in improved visualization of the visual indicator. For example, if the collar is metal plated, damping may be decreased, resulting in improved visualization of the visual indicator. For example, if the collar is plated with metal using electroplating, damping may be decreased, resulting in improved visualization of the visual indicator. For example, if the collar is plated with metal using electroless plating, damping may be decreased, resulting in improved visualization of the visual indicator. For example, if the collar is nickel plated, for example using nickel electroplating, or for example using electroless nickel plating, damping may be decreased, resulting in improved visualization of the visual indicator.

[0138] The needle tube may be composed of 304 stainless steel. The hub may be composed of plastic. The plastic that the hub may be composed of may be polycarbonate. The collar may be composed of H02 half hard C69300 brass. It may be useful if the mass of the collar is large enough to cause decreased damping, resulting in improved visualization of the visual indicator. The mass of the collar should not be too large, because too large of a mass may make it difficult to use the hypodermic needle. For example, if the needle tube has an outer diameter of 1.27 millimeters, the length of the needle tube from the needle tip to the collar is 70 millimeters, and the length of the needle tube from the collar to the hub is 1.0 millimeters, a mass of the collar in the range of 1.5 to 7.5 grams, such as 3.5 grams, may work well. For example, a disc shaped collar with a bore connecting two flat faces, with an outer diameter of 12 millimeters, and a length of 4 millimeters between the two flat faces, resulting in a mass of approximately 3.5 grams, may work well. See, for example, FIG. 23.

[0139] A separately acquired B-mode image of the needle tip in tissue may visualize tissue. A compound image created by combining the asynchronous resonance image and the B-mode imagemay visualize the visual indicator and the tissue, such that the position of the needle tip relative to the tissue may be visualized. Visualization of the visual indicator may be improved because the collar is a metal part joined to the needle tube, which causes decreased damping. Visualization of the visual indicator may be improved due to decreased damping caused by not gripping the collar.

[0140] FIG. 4 is a block diagram of a hardware configuration of an example device that may function as a process control device / logic controller, such as the PCB and / or processor of a powered personal care (e.g., razor, toothbrush, water pick, etc.) device, and / or a charging device, among other devices. The hardware configuration 400 may be operable to facilitate delivery of information from an internal server of a device. 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, for example, be interconnected using 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 the processor 410 can be a multi -threaded processor. The processor 410 can be capable of processing instructions stored in the memory 420 and / or on the storage device 430.

[0141] In one or more scenarios, a first PCB may comprise / interface with ultrasound sound system / equipment 480, and / or camera(s) 460, while a second PCB (not shown) may comprise / interface with the processor 410 and / or other circuit elements described herein. In one or more scenarios, a PCB may comprise / interface with some or all of the ultrasound sound system / equipment 480, camera 460, processor(s) 410, and other circuit elements described herein. 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 ultrasound scanners capable of providing / configured to provide at least the ultrasound probing and / or imaging as described herein.

[0142] The memory 420 can store information within the hardware configuration 400. The memory 420 can be a computer-readable medium (CRM), for example, a non-transitory CRM. The memory 420 can be a volatile memory unit, and / or can be a non-volatile memory unit.

[0143] The storage device 430 can be capable of providing 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, for example, include a hard disk device, an optical disk device, flash memory and / or some other large capacity storage device. The storage device 430 can be a device external to the hardware configuration 400.

[0144] The input / output device 440 may provide input / output operations for the hardware configuration 400. The input / output device 440 (e.g., a transceiver device) can 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 device can include driver devices configured to send communications to, and / or receive communications from one or more networks (not shown). The input / output device 400 may be in communication with one or more input / output modules (not shown) that may be proximate to the hardware configuration 400 and / or may be remote from the hardware configuration 400. The one or more output modules may provide input / output functionality in the digital signal form, discrete signal form, TTL form, analog signal form, serial communication protocol, fieldbus protocol communication and / or other open or proprietary communication protocol, and / or the like. The input / output device can include driver devices configured to send communications to, and / or receive communications from one or more networks. The input / output device 440 may be in communication with at least one display device 484. The display device 484 may display any of the ultrasound generated images described herein.

[0145] The camera device 460 may provide digital video input / output capability for the hardware configuration 400. The camera device 460 may communicate with any of the elements of the hardware configuration 400, perhaps for example via system bus 450. The camera device 460 may capture digital images and / or may scan images / light of various kinds, such as Universal Product Code (UPC) codes and / or Quick Response (QR) codes, and / or sonography images, for example, among other images as described herein. In one or more scenarios, the camera device 460 may be the same and / or substantially similar to any of the other camera devices as may be described herein.

[0146] The camera device 460 may include at least one microphone device and / or at least one speaker device (not shown). The input / output of the camera device 460 may include audio signals / packets / components, perhaps for example separate / separable from, or in some (e.g., separable) combination with, the video signals / packets / components the camera device 460.

[0147] The camera device 460 may also detect the presence of one or more subjects that may be proximate to the camera device 460 and / or may be in the same general space (e.g., the same room, delimited area, etc.) as the camera device 460. The camera device 460 may gauge a general activity level (e.g., high activity, medium activity, and / or low activity) of one or more subjects that may be detected by the camera device 460. The camera device 460 may detect one or more generalcharacteristics (e.g., height, body shape, skin color, pulse, heart rate, breathing count, etc.) of the one or more subjects detected by the camera device 460. The camera device 460 may be configured to recognize one or more specific subjects, for example.

[0148] The camera device 460 may be in wired and / or wireless communication with the hardware configuration 400. In one or more scenarios, the camera device 460 may be external to the hardware configuration 400. In one or more scenarios, the camera device 460 may be internal to the hardware configuration 400.

[0149] In view of FIG. 1 to FIG. 23, one or more devices, techniques, methods, and / or systems described herein may comprise a hypodermic needle that may be configured for detection in sonographic imaging of tissue. The needle may comprise a needle tube. The needle tube may comprise an outer surface, a proximal end, and / or a distal end. The distal end may comprise a needle tip. The needle may comprise a hub. The hub may comprise a hub bore proximate to a center of the hub. The hub may be in fixed connection to the outer surface of the needle tube at least proximate to the hub bore. The needle may comprise a collar. The collar may comprise a collar bore proximate to a center of the collar. The collar may be in fixed connection to the outer surface of the needle at least proximate to the collar bore. The collar may be configured to decrease damping of a radiated wave propagated by the needle tip in response to sonographic energy excitation transmitted into the tissue.

[0150] In one or more scenarios, the fixed connection between the hub bore and the outer surface of the needle tube may be configured such that the hub bore and the needle tube are connected as a shaft and hole pairing.

[0151] In one or more scenarios, the fixed connection between the collar bore and the outer surface of the needle tube may be configured such that the collar bore and the needle tube are connected as a shaft and hole pairing.

[0152] In one or more scenarios, the fixed connection between the hub bore and the outer surface of the needle tube may be configured such that a first joint is formed between the outer surface of the needle tube and a surface of the hub bore.

[0153] In one or more scenarios, the fixed connection between the collar bore and the outer surface of the needle tube may be configured such that a second joint is formed between the outer surface of the needle tube and a surface of the collar bore. In one or more scenarios, the second joint may be a friction joint. In one or more scenarios, the friction joint may be at least one of: an interference fit joint, or a staked joint.

[0154] In one or more scenarios, the first joint may form a first rigid fixed connection between the outer surface of the needle tube and the hub.

[0155] In one or more scenarios, the second joint may form a second rigid fixed connection between the outer surface of the needle tube and the collar.

[0156] In one or more scenarios, the second rigid fixed connection may provide for a fixed position of the collar relative to the needle tube. The second rigid fixed connection may cause a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

[0157] In one or more scenarios, the second rigid fixed connection may prevent movement of the collar relative to the needle tube at least with mechanically unassisted manual force.

[0158] In one or more scenarios, an outer shape of the collar may be cylindrical.

[0159] In one or more scenarios, the needle tube may be composed of, at least in part, stainless steel.

[0160] In one or more scenarios, the collar may be composed of, at least in part, metal. In one or more scenarios, the collar may be metal coated. In one or more scenarios, the metal or a metal- coated composition may be at least one of brass, or nickel.

[0161] In one or more scenarios, the at least partial metal or metal-coated composition of the collar may cause a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

[0162] In one or more scenarios, the proximal end of the needle tube and the distal end of the needle tube may extend beyond the collar bore.

[0163] In one or more scenarios, the sonographic energy excitation may be provided by an ultrasound scanner.

[0164] One or more devices, techniques, methods, and / or systems described herein may comprise a sonographic system for imaging in tissue. The system may comprise an ultrasound scanner. The ultrasound scanner may comprise a display device and / or a processor. The processor may be configured to transmit sonographic energy into the tissue. The processor may be configured to process a time-delayed based image of the tissue. The processor may be configured to process a non-time delayed image of the tissue. The processor may be configured to generate a compound image of the tissue based on the time-delayed based image of the tissue and the nontime delayed based image of the tissue. The processor may be configured to render the compoundimage of the tissue on the display device. The system may comprise a hypodermic needle configured for insertion into the tissue.

[0165] The needle may comprise a needle tube. The needle tube may comprise an outer surface, a proximal end, and / or a distal end. The distal end may comprise a needle tip. The needle may comprise a hub. The hub may comprise a hub bore proximate to a center of the hub. The hub may be in fixed connection to the outer surface of the needle tube at least proximate to the hub bore. The needle may comprise a collar. The collar may comprise a collar bore proximate to a center of the collar. The collar may be in fixed connection to the outer surface of the needle at least proximate to the collar bore. The collar may be configured to decrease damping of a radiated wave propagated by the needle tip in response to the sonographic energy excitation transmitted into the tissue. The compound image may include at least one visual indicator of the needle tip. The decrease damping may cause an improvement in visualization of the visual indicator relative to a visual indicator corresponding to a hypodermic needle configured without a collar.

[0166] In one or more scenarios, the processor may be further configured such that to process the time-delayed based image of the tissue comprises an acquisition of the time-delayed based image with use of a time delay between a start of a pulse transmission and a start of an echo receive period.

[0167] In one or more scenarios, the processor may be further configured such that to process the time-delayed based image of the tissue comprises configuration of a time after a start of a pulse transmission to correspond to an image depth of zero.

[0168] In one or more scenarios, the processor may be further configured to process the time- delayed based image of the tissue using a time delay between a pulse transmission and receiving a radiated wave propagated by the needle tip that is long enough that tissue echoes dissipate, such that a relatively adequate signal created by the radiated wave propagated by the needle tip is recorded.

[0169] In one or more scenarios, the fixed connection between the hub bore and the outer surface of the needle tube may be configured such that the hub bore and the needle tube are connected as a shaft and hole pairing.

[0170] In one or more scenarios, the fixed connection between the collar bore and the outer surface of the needle tube may be configured such that the collar bore and the needle tube are connected as a shaft and hole pairing.

[0171] In one or more scenarios, the fixed connection between the hub bore and the outer surfaceof the needle tube may be configured such that a first joint is formed between the outer surface of the needle tube and a surface of the hub bore.

[0172] In one or more scenarios, the fixed connection between the collar bore and the outer surface of the needle tube may be configured such that a second joint is formed between the outer surface of the needle tube and a surface of the collar bore.

[0173] In one or more scenarios, the second joint may be a friction joint. In one or more scenarios, the friction joint may be at least one of: an interference fit joint, or a staked joint.

[0174] In one or more scenarios, the first joint may form a first rigid fixed connection between the outer surface of the needle tube and the hub.

[0175] In one or more scenarios, the second joint may form a second rigid fixed connection between the outer surface of the needle tube and the collar. In one or more scenarios, the second rigid fixed connection may provide for a fixed position of the collar relative to the needle tube. The second rigid fixed connection may cause a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation. In one or more scenarios, the second rigid fixed connection may prevent movement of the collar relative to the needle tube at least with mechanically unassisted manual force.

[0176] In one or more scenarios, an outer shape of the collar may be cylindrical.

[0177] In one or more scenarios, the needle tube may be composed of, at least in part, stainless steel.

[0178] In one or more scenarios, the collar may be composed of, at least in part, metal. In one or more scenarios, the collar may be metal-coated. In one or more scenarios, the metal or a metal- coated composition may be at least one of: brass, or nickel. In one or more scenarios, the at least partial metal or metal-coated composition of the collar may cause a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

[0179] In one or more scenarios, the proximal end of the needle tube and the distal end of the needle tube may extend beyond the collar bore.

[0180] In one or more scenarios, the visual indicator may be a ringdown artifact.

[0181] One or more devices, techniques, methods, and / or systems described herein may comprise a method for imaging in tissue. The method may comprise transmitting, by an ultrasound scanner, sonographic energy into the tissue. The method may comprise processing, by the ultrasound scanner, a time-delayed based image of the tissue. The method may comprise processing, by the ultrasound scanner, a non-time delayed image of the tissue. The method maycomprise generating, by the ultrasound scanner, a compound image of the tissue based on the time- delayed based image of the tissue and the non-time delayed based image of the tissue. The method may comprise rendering, by the ultrasound system, the compound image of the tissue on a display device. The compound image may comprise a visual indicator of a needle tip of a hypodermic needle inserted into the tissue.

[0182] The hypodermic needle may comprise a needle tube. The needle tube may comprise an outer surface, a proximal end, and / or a distal end. The distal end may comprise the needle tip. The needle may comprise a hub. The hub may comprise a hub bore proximate to a center of the hub. The hub may be in fixed connection to the outer surface of the needle tube at least proximate to the hub bore. The needle may comprise a collar. The collar may comprise a collar bore proximate to a center of the collar. The collar may be in fixed connection to the outer surface of the needle at least proximate to the collar bore. The collar may decrease damping of a radiated wave propagated by the needle tip in response to the sonographic energy excitation transmitted into the tissue. The decreasing damping may cause an improvement in visualization of the visual indicator relative to a visual indicator corresponding to a hypodermic needle configured without a collar.

[0183] In one or more scenarios, the processing, by the ultrasound scanner, the time-delayed based image of the tissue may further comprise acquiring the time-delayed based image using a time delay between a start of a pulse transmission and a start of an echo receive period.

[0184] In one or more scenarios, the processing, by the ultrasound scanner, the time-delayed based image of the tissue may be such that a time after a start of a pulse transmission is configured to correspond to an image depth of zero.

[0185] In one or more scenarios, the processing, by the ultrasound scanner, the time-delayed based image of the tissue may be such that a time delay between a pulse transmission and receiving a radiated wave propagated by the needle tip is long enough that tissue echoes dissipate, such that a relatively adequate signal created by the radiated wave propagated by the needle tip is recorded.

[0186] In one or more scenarios, the fixed connection between the hub bore and the outer surface of the needle tube may be configured such that the hub bore and the needle tube are connected as a shaft and hole pairing.

[0187] In one or more scenarios, the fixed connection between the collar bore and the outer surface of the needle tube may be configured such that the collar bore and the needle tube are connected as a shaft and hole pairing.

[0188] In one or more scenarios, the fixed connection between the hub bore and the outer surface of the needle tube may be configured such that a first joint is formed between the outer surface of the needle tube and a surface of the hub bore.

[0189] In one or more scenarios, the fixed connection between the collar bore and the outer surface of the needle tube may be configured such that a second joint is formed between the outer surface of the needle tube and a surface of the collar bore.

[0190] In one or more scenarios, the second joint may be a friction joint. In one or more scenarios, the friction joint may be at least one of: an interference fit joint, or a staked joint.

[0191] In one or more scenarios, the first joint may form a first rigid fixed connection between the outer surface of the needle tube and the hub.

[0192] In one or more scenarios, the second joint may form a second rigid fixed connection between the outer surface of the needle tube and the collar. In one or more scenarios, the second rigid fixed connection may provide for a fixed position of the collar relative to the needle tube. The second rigid fixed connection may cause a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation. In one or more scenarios, the second rigid fixed connection may prevent movement of the collar relative to the needle tube at least with mechanically unassisted manual force.

[0193] In one or more scenarios, an outer shape of the collar may be cylindrical.

[0194] In one or more scenarios, the needle tube may be composed of, at least in part, stainless steel. In one or more scenarios, the collar may be composed of, at least in part, metal. In one or more scenarios, the collar may be metal-coated. In one or more scenarios, the metal or a metal- coated composition may be at least one of: brass, or nickel. In one or more scenarios, the at least partial metal or metal-coated composition of the collar causes a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

[0195] In one or more scenarios, the proximal end of the needle tube and the distal end of the needle tube may extend beyond the collar bore.

[0196] In one or more scenarios, the visual indicator may be a ringdown artifact.

[0197] While the inventions have been described with respect to specific examples including presently preferred modes of carrying out the inventions, those skilled in the art will appreciate that there are numerous variations and permutations of the herein described systems and techniques. It is to be understood that other embodiments may be utilized and structural and functional modifications may be made without departing from the scope of the present inventions.Thus, the spirit and scope of the inventions should be construed broadly as set forth in the appended claims.

[0198] The subject matter of this disclosure, and components thereof, can be realized by instructions that upon execution cause one or more processing devices to carry out the processes and / or functions described herein. Such instructions can, for example, comprise interpreted instructions, such as script instructions, e.g., JavaScript or ECMAScript instructions, or executable code, and / or other instructions stored in a computer readable medium. C ++, C#, and / or C, Python scripts and / or Zephyr RTOS may be used.

[0199] Implementations of the subject matter and / or the functional operations described in this specification and / or the accompanying figures can be provided in digital electronic circuitry, in computer software, firmware, and / or hardware, including the structures disclosed in this specification and their structural equivalents, and / or in combinations of one or more of them. The subject matter described in this specification can be implemented as one or more computer program products, e.g., one or more modules of computer program instructions encoded on a tangible program carrier for execution by, and / or to control the operation of, data processing apparatus.

[0200] A computer program (also known as a program, software, software application, script, or code) can be written in any form of programming language, including compiled or interpreted languages, and / or declarative or procedural languages. It can be deployed in any form, including as a stand-alone program or as a module, component, subroutine, and / or other unit suitable for use in a computing environment. A computer program may or might not correspond to a file in a file system. A program can be stored in a portion 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 multiple coordinated files (e.g., files that store one or more modules, sub programs, or portions of code). A computer program can be deployed to be executed on one computer or on multiple computers that may be located at one site or distributed across multiple sites and / or interconnected by a communication network.

[0201] Processors described herein may be any central processing unit (CPU), microprocessor, micro-controller, computational, or programmable device or circuit configured for executing computer program instructions (e.g., code). Various processors may be embodied in computer and / or server hardware of any suitable type (e.g., desktop, laptop, notebook, tablets, cellular phones, etc.) and may include all the usual ancillary components necessary to form a functionaldata processing device including without limitation a bus, software and data storage such as volatile and non-volatile memory, input / output devices, graphical user interfaces (GUIs), removable data storage, and wired and / or wireless communication interface devices including WiFi™, Bluetooth™, LAN, cellular, satellite, etc.

[0202] Computer-executable instructions or programs (e.g., software or code) and data described herein may be programmed into and tangibly embodied in a non-transitory computer-readable medium that is accessible to and retrievable by a respective processor as described herein which configures and directs the processor to perform the desired functions and processes by executing the instructions encoded in the medium. A device embodying a programmable processor configured to such non-transitory computer-executable instructions or programs may be referred to as a “programmable device”, or “device”, and multiple programmable devices in mutual communication may be referred to as a “programmable system.” It should be noted that non- transitory “computer-readable medium” as described herein may include, without limitation, any suitable volatile or non-volatile memory including random access memory (RAM) and various types thereof, read-only memory (ROM) and various types thereof, USB flash memory, and magnetic or optical data storage devices (e.g., intemal / extemal hard disks, floppy discs, magnetic tape CD-ROM, DVD-ROM, optical disk, ZIP™ drive, Blu-ray disk, and others), which may be written to and / or read by a processor operably connected to the medium.

[0203] The processes and / or logic flows described in this specification and / or in the accompanying figures may be performed by one or more programmable processors executing one or more computer programs to perform functions by operating on input data and / or generating output, thereby tying the process to a particular machine (e.g., a machine programmed to perform the processes described herein). The processes and / or logic flows can also be performed by, and apparatus can also be implemented as, special purpose logic circuitry, e g., an FPGA (field programmable gate array) and / or an ASIC (application specific integrated circuit).

[0204] Computer readable media suitable for storing computer program instructions and / or data may include all forms 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 the memory can be supplemented by, or incorporated in, special purpose logic circuitry.

[0205] While this specification and the accompanying figures contain many specific implementation details, these should not be construed as limitations on the scope of any invention and / or of what may be claimed, but rather as descriptions of features that may be specific to described example implementations. Certain features that are described in this specification in the context of separate implementations can also be implemented in combination in perhaps one implementation. Various features that are described in the context of perhaps one implementation can also be implemented in multiple combinations separately or in any suitable sub-combination. Although features may be described above as acting in certain combinations and / or perhaps even (e g., initially) claimed as such, one or more features from a claimed combination can in some cases be excised from the combination. The claimed combination may be directed to a subcombination and / or variation of a sub-combination.

[0206] While operations may be depicted in the drawings in an order, this should not be understood as requiring that such operations be performed in the particular order shown and / or in sequential order, and / or that all illustrated operations be performed, to achieve useful outcomes. The described program components and / or systems can generally be integrated together in a single software product and / or packaged into multiple software products.

[0207] Examples of the subject matter described in this specification have been described. The actions recited in the claims can be performed in a different order and still achieve useful outcomes, unless expressly noted otherwise. For example, the processes depicted in the accompanying figures do not require the particular order shown, and / or sequential order, to achieve useful outcomes. Multitasking and parallel processing may be advantageous in one or more scenarios.

[0208] While the present disclosure has been illustrated and described in detail in the drawings and foregoing description, the same is to be considered as illustrative and not restrictive in character, it being understood that only certain examples have been shown and described, and that all changes and modifications that come within the spirit of the present disclosure are desired to be protected.

Claims

CLAIMSWHAT IS CLAIMED IS:

1. A hypodermic needle configured for detection in sonographic imaging of tissue, the needle comprising: a needle tube, the needle tube comprising: an outer surface; a proximal end; and a distal end, the distal end comprising a needle tip; a hub, the hub comprising a hub bore proximate to a center of the hub, the hub being in fixed connection to the outer surface of the needle tube at least proximate to the hub bore; and a collar, the collar comprising a collar bore proximate to a center of the collar, the collar being in fixed connection to the outer surface of the needle at least proximate to the collar bore, the collar configured to decrease damping of a radiated wave propagated by the needle tip in response to sonographic energy excitation transmitted into the tissue.

2. The needle of claim 1, wherein the fixed connection between the hub bore and the outer surface of the needle tube is configured such that the hub bore and the needle tube are connected as a shaft and hole pairing.

3. The needle of any of claim 1 to claim 2, wherein the fixed connection between the collar bore and the outer surface of the needle tube is configured such that the collar bore and the needle tube are connected as a shaft and hole pairing.

4. The needle of any of claim 1 to claim 3, wherein the fixed connection between the hub bore and the outer surface of the needle tube is configured such that a first joint is formed between the outer surface of the needle tube and a surface of the hub bore.

5. The needle of any of claim 1 to claim 4, wherein the fixed connection between the collar bore and the outer surface of the needle tube is configured such that a second joint is formed between the outer surface of the needle tube and a surface of the collar bore.

6. The needle of claim 5, wherein the second joint is a friction joint.

7. The needle of claim 6, wherein the friction joint is at least one of: an interference fit joint, or a staked joint.

8. The needle of any of claim 4 to claim 7, wherein the first joint forms a first rigid fixed connection between the outer surface of the needle tube and the hub.

9. The needle of any of claim 4 to claim 8, wherein the second joint forms a second rigid fixed connection between the outer surface of the needle tube and the collar.

10. The needle of claim 9, wherein the second rigid fixed connection provides for a fixed position of the collar relative to the needle tube, and the second rigid fixed connection causes a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

11. The needle of any of claim 9 to claim 10, wherein the second rigid fixed connection prevents movement of the collar relative to the needle tube at least with mechanically unassisted manual force.

12. The needle of any of claim 1 to claim 11, wherein an outer shape of the collar is cylindrical.

13. The needle of any of claim 1 to claim 12, wherein the needle tube is composed of, at least in part, stainless steel.

14. The needle of any of claim 1 to claim 13, wherein the collar is composed of, at least in part, metal.

15. The needle of any of claim 1 to claim 14, wherein the collar is metal coated.

16. The needle of any of claim 14 to claim 15, wherein the metal or a metal-coated composition is at least one of: brass, or nickel.

17. The needle of any of claim 14 to claim 16, wherein the at least partial metal or metal-coated composition of the collar causes a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

18. The needle of any of claim 1 to claim 17, wherein the proximal end of the needle tube and the distal end of the needle tube extend beyond the collar bore.

19. The needle of any of claim 1 to claim 18, wherein the sonographic energy excitation is provided by an ultrasound scanner.

20. A sonographic system for imaging in tissue, the system comprising: an ultrasound scanner, comprising: a display device; and a processor, configured at least to: transmit sonographic energy into the tissue; process a time-delayed based image of the tissue; process a non-time delayed image of the tissue; generate a compound image of the tissue based on the time-delayed based image of the tissue and the non-time delayed based image of the tissue; and render the compound image of the tissue on the display device; and a hypodermic needle configured for insertion into the tissue, the needle comprising: a needle tube, the needle tube comprising: an outer surface; a proximal end; and a distal end, the distal end comprising a needle tip; a hub, the hub comprising a hub bore proximate to a center of the hub, the hub being in fixed connection to the outer surface of the needle tube at least proximate to the hub bore; and a collar, the collar comprising a collar bore proximate to a center of the collar, the collar being in fixed connection to the outer surface of the needle at least proximate to the collar bore, the collar configured to decrease damping of a radiated wave propagated by the needle tip in response to the sonographic energy excitation transmitted into the tissue, the compound imageincluding at least one visual indicator of the needle tip, and the decrease damping causes an improvement in visualization of the visual indicator relative to a visual indicator corresponding to a hypodermic needle configured without a collar.

21. The system of claim 20, wherein the processor is further configured such that to process the time-delayed based image of the tissue comprises an acquisition of the time-delayed based image with use of a time delay between a start of a pulse transmission and a start of an echo receive period.

22. The system of claim 20, wherein the processor is further configured such that to process the time-delayed based image of the tissue comprises configuration of a time after a start of a pulse transmission to correspond to an image depth of zero.

23. The system of claim 20, wherein the processor is further configured to process the time-delayed based image of the tissue using a time delay between a pulse transmission and receiving a radiated wave propagated by the needle tip that is long enough that tissue echoes dissipate, such that a relatively adequate signal created by the radiated wave propagated by the needle tip is recorded.

24. The system of any of claim 20 to claim 23, wherein the fixed connection between the hub bore and the outer surface of the needle tube is configured such that the hub bore and the needle tube are connected as a shaft and hole pairing.

25. The system of any of claim 20 to claim 24, wherein the fixed connection between the collar bore and the outer surface of the needle tube is configured such that the collar bore and the needle tube are connected as a shaft and hole pairing.

26. The system of any of claim 20 to claim 25, wherein the fixed connection between the hub bore and the outer surface of the needle tube is configured such that a first joint is formed between the outer surface of the needle tube and a surface of the hub bore.

27. The system of any of claim 20 to claim 26, wherein the fixed connection between the collar bore and the outer surface of the needle tube is configured such that a second joint is formed between the outer surface of the needle tube and a surface of the collar bore.

28. The system of claim 27, wherein the second joint is a friction joint.

29. The system of claim 28, wherein the friction joint is at least one of: an interference fit joint, or a staked joint.

30. The system of any of claim 26 to claim 29, wherein the first joint forms a first rigid fixed connection between the outer surface of the needle tube and the hub.

31. The system of any of claim 27 to claim 30, wherein the second joint forms a second rigid fixed connection between the outer surface of the needle tube and the collar.

32. The system of claim 31, wherein the second rigid fixed connection provides for a fixed position of the collar relative to the needle tube, and the second rigid fixed connection causes a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

33. The system of any of claim 31 to claim 32, wherein the second rigid fixed connection prevents movement of the collar relative to the needle tube at least with mechanically unassisted manual force.

34. The system of any of claim 20 to claim 33, wherein an outer shape of the collar is cylindrical.

35. The system of any of claim 20 to claim 34, wherein the needle tube is composed of, at least in part, stainless steel.

36. The system of any of claim 20 to claim 35, wherein the collar is composed of, at least in part, metal.

37. The system of any of claim 20 to claim 36, wherein the collar is metal-coated.

38. The system of any of claim 36 to claim 37, wherein the metal or a metal-coated composition is at least one of: brass, or nickel.

39. The system of any of claim 36 to claim 38, wherein the at least partial metal or metal-coated composition of the collar causes a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

40. The system of any of claim 20 to claim 39, wherein the proximal end of the needle tube and the distal end of the needle tube extend beyond the collar bore.

41. The system of any of claim 20 to claim 40, wherein the visual indicator is a ringdown artifact.

42. A method for imaging in tissue, the method comprising: transmitting, by an ultrasound scanner, sonographic energy into the tissue; processing, by the ultrasound scanner, a time-delayed based image of the tissue; processing, by the ultrasound scanner, a non-time delayed image of the tissue; generating, by the ultrasound scanner, a compound image of the tissue based on the time- delayed based image of the tissue and the non-time delayed based image of the tissue; andrendering, by the ultrasound system, the compound image of the tissue on a display device, the compound image comprising a visual indicator of a needle tip of a hypodermic needle inserted into the tissue, the hypodermic needle comprising: a needle tube, the needle tube comprising: an outer surface; a proximal end; and a distal end, the distal end comprising the needle tip; a hub, the hub comprising a hub bore proximate to a center of the hub, the hub being in fixed connection to the outer surface of the needle tube at least proximate to the hub bore; and a collar, the collar comprising a collar bore proximate to a center of the collar, the collar being in fixed connection to the outer surface of the needle at least proximate to the collar bore, the collar decreasing damping of a radiated wave propagated by the needle tip in response to the sonographic energy excitation transmitted into the tissue, the decreasing damping causing an improvement in visualization of the visual indicator relative to a visual indicator corresponding to a hypodermic needle configured without a collar.

43. The method of claim 42, wherein the processing, by the ultrasound scanner, the time-delayed based image of the tissue further comprises: acquiring the time-delayed based image using a time delay between a start of a pulse transmission and a start of an echo receive period.

44. The method of claim 42, wherein the processing, by the ultrasound scanner, the time-delayed based image of the tissue is such that a time after a start of a pulse transmission is configured to correspond to an image depth of zero.

45. The method of claim 42, wherein the processing, by the ultrasound scanner, the time-delayed based image of the tissue is such that a time delay between a pulse transmission and receiving a radiated wave propagated by the needle tip is long enough that tissue echoes dissipate, such that a relatively adequate signal created by the radiated wave propagated by the needle tip is recorded.

46. The method of any of claim 42 to claim 45, wherein the fixed connection between the hub bore and the outer surface of the needle tube is configured such that the hub bore and the needle tube are connected as a shaft and hole pairing.

47. The method of any of claim 42 to claim 46, wherein the fixed connection between the collar bore and the outer surface of the needle tube is configured such that the collar bore and the needle tube are connected as a shaft and hole pairing.

48. The method of any of claim 42 to claim 47, wherein the fixed connection between the hub bore and the outer surface of the needle tube is configured such that a first joint is formed between the outer surface of the needle tube and a surface of the hub bore.

49. The method of any of claim 42 to claim 48, wherein the fixed connection between the collar bore and the outer surface of the needle tube is configured such that a second joint is formed between the outer surface of the needle tube and a surface of the collar bore.

50. The method of claim 49, wherein the second joint is a friction joint.

51. The method of claim 50, wherein the friction joint is at least one of: an interference fit joint, or a staked joint.

52. The method of any of claim 48 to claim 51, wherein the first joint forms a first rigid fixed connection between the outer surface of the needle tube and the hub.

53. The method of any of claim 49 to claim 52, wherein the second joint forms a second rigid fixed connection between the outer surface of the needle tube and the collar.

54. The method of claim 53, wherein the second rigid fixed connection provides for a fixed position of the collar relative to the needle tube, and the second rigid fixed connection causes a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

55. The method of any of claim 53 to claim 54, wherein the second rigid fixed connection prevents movement of the collar relative to the needle tube at least with mechanically unassisted manual force.

56. The method of any of claim 42 to claim 55, wherein an outer shape of the collar is cylindrical.

57. The method of any of claim 42 to claim 56, wherein the needle tube is composed of, at least in part, stainless steel.

58. The method of any of claim 42 to claim 57, wherein the collar is composed of, at least in part, metal.

59. The method of any of claim 42 to claim 58, wherein the collar is metal-coated.

60. The method of any of claim 58 to claim 59, wherein the metal or a metal-coated composition is at least one of: brass, or nickel.

61. The method of any of claim 58 to claim 60, wherein the at least partial metal or metal-coated composition of the collar causes a further decrease in damping of the radiated wave propagated by the needle tip in response to the sonographic energy excitation.

62. The method of any of claim 42 to claim 61, wherein the proximal end of the needle tube and the distal end of the needle tube extend beyond the collar bore.

63. The method of any of claim 42 to claim 62, wherein the visual indicator is a ringdown artifact.

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