Patent Application
20240350153
All publications and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication or patent application was specifically and individually indicated to be incorporated by reference.
This disclosure relates to histotripsy systems configured to produce acoustic cavitation, methods, devices, and procedures for the minimally and non-invasive treatment of healthy, diseased and/or injured tissue. The histotripsy systems and methods described herein may include transducers, drive electronics, positioning systems including robotics, imaging systems, patient coupling systems, and integrated treatment planning and control software to provide comprehensive treatment and therapy for soft and/or hard tissues in a patient. In particular, soft tissues such as organs or structures found within the abdominal cavity (e.g., liver, kidney, spleen, pancreas, stomach, colon, small intestine), pelvic and reproductive tissues/organs (e.g., prostate, uterus), lungs, brain, esophagus, muscles, tendons/ligaments, hard tissues such as bone, external tissues such as dermis/skin and tissues found on, and/or partially within skin surface, implants, medical devices, are envisioned for use with Histotripsy treatment and therapy.
Histotripsy, or pulsed ultrasound cavitation therapy, is a technology where extremely short, intense bursts of acoustic energy induce controlled cavitation (microbubble formation) within the focal volume. The vigorous expansion and collapse of these microbubbles mechanically homogenizes cells and tissue structures within the focal volume. This is a very different end result than the coagulative necrosis characteristic of thermal ablation. To operate within a non-thermal, Histotripsy realm, it is necessary to deliver acoustic energy in the form of high amplitude very short acoustic pulses, typically with low duty cycle.
Compared with conventional focused ultrasound technologies, histotripsy has important advantages: 1) the destructive process at the focus is mechanical, not thermal; 2) cavitation appears bright on ultrasound imaging thereby confirming correct targeting and localization of treatment; 3) treated tissue generally, but not always, appears darker (more hypoechoic) on ultrasound imaging, so that the operator knows what has been treated; and 4) Histotripsy produces lesions in a controlled and precise manner. It is important to emphasize that unlike thermal ablative technologies such as microwave, radiofrequency, high-intensity focused ultrasound (HIFU) cryo or radiation, Histotripsy relies on the mechanical action of cavitation for tissue destruction and not on heat, cold or ionizing energy. Despite these clear advantages improvements in methods and systems are always desired.
One aspect of the disclosure is directed to a histotripsy system including an ultrasound imaging probe; an ultrasound therapy transducer coupled to the ultrasound imaging probe. The histotripsy system also includes a robotic arm configured to orient the ultrasound imaging probe and the ultrasound therapy transducer about a patient; a display operably connected to imaging probe; a memory, storing thereon instructions that when executed by a processor operably connected to the memory: receive live ultrasound images from the ultrasound imaging probe; present the live ultrasound images on a user interface in the display; receive via the user interface an input to alter a shape of a treatment contour around a treatment area in the live ultrasound images; present a contour line representative of the treatment contour on the ultrasound images in the user interface; receive via the user interface an input of a size of a margin around the treatment area; present a margin line representative of the margin on the ultrasound images in the user interface; determine survey points at locations where X, Y, and Z axes bisect the margin line in an XZ plane and a YZ plane; receive an input to drive the ultrasound therapy transducer to a location where a focal point of the ultrasound therapy transducer is at one of the survey points, and determine whether resistance to movement of the ultrasound therapy transducer exceeds a threshold. Other embodiments of this aspect include corresponding computer systems, apparatus, and computer programs recorded on one or more computer storage devices, each configured to perform the actions of the methods and systems described herein.
Implementations of this aspect of the disclosure may include one or more of the following features. The histotripsy system where receipt via the user interface of an input to alter the shape of the treatment contour around a treatment area occurs in live ultrasound images in the XZ plane and in the YZ plane. The input to drive the ultrasound therapy transducer is received via the user interface in the display. The input to drive the ultrasound therapy transducer is received for each survey point. Upon determination that the resistance to movement of the ultrasound therapy transducer in driving to reach all of the survey points does not exceed a threshold, a planned therapy is accepted and stored in the memory. Upon determination that the resistance to movement of the ultrasound therapy transducer in driving to reach any of the survey points exceeds a threshold, the instructions stored in memory and executed by the processor cause the user interface to present mitigation instructions. The histotripsy system further including presenting a representation of the contour line and the survey points in a separate field in the user interface. The input to drive the therapy transducer is received via the representation of the contour line and survey points in the separate field in the user interface. The indicator is depicted upon movement of the therapy transducer to a location at which the focal point coincides with the survey point. The instructions when executed by the processor receive in input of a location of an intersection of a muscle layer and a fat layer in the live ultrasound images. The instructions when executed by the processor cause activation of knobs which when manipulated adjust a parameter displayed in an indicator on the user interface. The knobs adjust the contour along the x, y, and z axes. The knobs adjust the size of the margin around the contour. The knobs adjust the focal point of the therapy transducer. Implementations of the described techniques may include hardware, a method or process, or computer software on a computer-accessible medium, including software, firmware, hardware, or a combination of them installed on the system that in operation causes or cause the system to perform the actions. One or more computer programs can be configured to perform particular operations or actions by virtue of including instructions that, when executed by data processing apparatus, cause the apparatus to perform the actions.
A further aspect of the disclosure is directed to a method of planning a histotripsy procedure. The method includes displaying live ultrasound images on a user interface. The method also includes moving an ultrasound assembly to a mark on a patient from which a treatment area within the patient can be observed in the live ultrasound images; presenting a contour line around a treatment area in the live ultrasound images on the user interface, adjusting the contour line in the live ultrasound images; identifying survey points where X, Y. and Z axes intersect the contour line in XZ plane and the YZ plane; displaying a margin around the contour line; displaying a focal point of an therapy transducer, where the therapy transducer is a component of the ultrasound assembly; driving the ultrasound assembly such that the focal point of the therapy transducer coincides with at least one of survey points; and detecting a resistance to movement of the ultrasound assembly as it moves to reach the at least one survey point. Other embodiments of this aspect include corresponding computer systems, apparatus, and computer programs recorded on one or more computer storage devices, each configured to perform the actions of the methods and systems described herein.
Implementations of this aspect of the disclosure may include one or more of the following features. The method further including comparing the resistance to movement to a threshold. The method further including altering a shape of the contour line around a treatment area in the live ultrasound images in the XZ plane and in the YZ plane. The ultrasound assembly is robotically driven to each survey point. Upon determination that the resistance to movement of the therapy transducer in driving to reach each of the survey points does not exceed a threshold, a planned therapy is accepted and stored in a memory. The method further including receiving in indication of a location of an intersection of a muscle layer and a fat layer in the live ultrasound images. Implementations of the described techniques may include hardware, a method or process, or computer software on a computer-accessible medium, including software, firmware, hardware, or a combination of them installed on the system that in operation causes or cause the system to perform the actions. One or more computer programs can be configured to perform particular operations or actions by virtue of including instructions that, when executed by data processing apparatus, cause the apparatus to perform the actions.
In one aspect, a histotripsy system is provided, comprising: an ultrasound imaging system; an ultrasound therapy transducer coupled to the ultrasound imaging system; a robotic arm configured to position the ultrasound imaging system and the ultrasound therapy transducer with respect to a patient and a treatment location, a display operably connected to the ultrasound imaging system; a memory, storing thereon instructions that when executed by a processor operably connected to the memory: receive real-time ultrasound images from the ultrasound imaging system; present the live ultrasound images on a user interface in the display; identify a target; receive via the user interface an input to alter a shape of a target contour around a treatment volume in the live ultrasound images; present a target contour line representative of the target contour on the ultrasound images in the user interface, receive via the user interface an input of a size of a margin around the target area; present a margin contour line representative of the margin contour on the ultrasound images in the user interface; determine survey points at locations where X, Y, and Z axes bisect the margin line in an XZ plane and a YZ plane, receive an input to drive the ultrasound therapy transducer to a location where a focal location of the ultrasound therapy transducer is at one of the survey points; and determine whether resistance to movement of the ultrasound therapy transducer exceeds a threshold.
In some aspects, receipt via the user interface of an input to alter the shape of the treatment contour around a treatment volume occurs in live ultrasound images in the XZ plane and in the YZ plane.
In some aspects, the input to drive the ultrasound therapy transducer is received via the user interface in the display.
In one aspect, the input to drive the ultrasound therapy transducer is received for each survey point.
In some aspects, upon determination that the resistance to movement of the ultrasound therapy transducer in driving to reach all of the survey points does not exceed a threshold, a planned therapy is accepted and stored in the memory.
In one aspect, upon determination that the resistance to movement of the ultrasound therapy transducer in driving to reach any of the survey points exceeds a threshold, the instructions stored in memory and executed by the processor cause the user interface to present mitigation instructions.
In some aspects, the system includes presenting a representation of the contour line and the survey points in a separate field in the user interface.
In another aspect, the input to drive the therapy transducer is received via the representation of the contour line and survey points in the separate field in the user interface.
The histotripsy system of claim 7, further comprising an indicator depicted on the survey point of the representation in the separate field on the user interface, wherein the indicator is depicted upon movement of the therapy transducer to a location at which the focal point coincides with the survey point.
In some aspects, the instructions when executed by the processor receive in input of a location of an intersection of a muscle layer and a fat layer in the live ultrasound images.
In other aspects, the instructions when executed by the processor cause activation of knobs which when manipulated adjust a parameter displayed in an indicator on the user interface.
In some aspects, the knobs adjust the contour along the X, Y, and Z axes.
In other aspects, the knobs adjust the size of the margin around the contour.
In some aspects, the knobs adjust the focal location of the therapy transducer.
A method of planning a histotripsy procedure is provided comprising: displaying live ultrasound images on a user interface; moving an ultrasound assembly to a mark on a patient from which a treatment area within the patient can be observed in the live ultrasound images; presenting a contour line around a treatment volume in the live ultrasound images on the user interface; adjusting the contour line in the live ultrasound images; identifying survey points where X, Y. and Z axes intersect the contour line in XZ plane and the YZ plane; displaying a margin around the contour line, displaying a focal point of a therapy transducer, wherein the therapy transducer is a component of the ultrasound assembly; driving the ultrasound assembly such that the focal point of the therapy transducer coincides with at least one of survey points; and detecting a resistance to movement of the ultrasound assembly as it moves to reach the at least one survey point.
In some aspects, the method includes comparing the resistance to movement to a threshold.
In other aspects, the method comprises altering a shape of the contour line around a treatment area in the live ultrasound images in the XZ plane and in the YZ plane.
In some aspects, the ultrasound assembly is robotically driven to each survey point.
In one aspect, upon determination that the resistance to movement of the therapy transducer in driving to reach each of the survey points does not exceed a threshold, a planned therapy is accepted and stored in a memory.
In some aspects, the method includes receiving in indication of a location of an intersection of a muscle layer and a fat layer in the live ultrasound images.
A method of histotripsy treatment is provided comprising: navigating a therapy transducer to align a focal point with a center of a planned treatment volume; activating histotripsy pulses, increasing a voltage associated with histotripsy pulses until bubble cloud/acoustic cavitation forms; marking a center of the bubble cloud; navigating the therapy transducer to a plurality of survey points about the planned treatment volume, wherein at each survey point the voltage associated with histotripsy pulses is activated and increased until a bubble cloud forms/is created; and initiating an automatic treatment plan, wherein the therapy transducer is robotically driven to a plurality of focal locations within the planned treatment volume and the histotripsy pulses is applied at each focal location.
In some aspects, the method includes interpolating an ultrasonic energy required for each focal location based on the voltage applied at each of the survey points and the center of the planned treatment volume.
In one aspect, the therapy transducer is driven to each focal location in a sequential pattern until all focal locations within the planned treatment volume has received an individualized histotripsy pulses.
In another aspect, the bubble cloud formed at each survey point is confirmed to coincide with the focal point of the therapy transducer.
In some aspects, following completion of the automatic treatment plan, deactivating a voltage knob associated with a source of the therapeutic energy.
In another aspect, the method includes confirming that all focal locations have received histotripsy pulses.
In some aspects, the method includes visualizing the planned treatment volume after completing the treatment plan to confirm complete treatment.
In one aspect, the visualization is performed with an ultrasound imaging probe.
In another aspect, a first survey point of the plurality of survey points to which the therapy transducer is navigated is a −Z survey point.
In one aspect, the method includes calculating an offset of the center of the bubble cloud and a focal point of the therapy transducer.
In some aspects, the method comprises utilizing the offset to calibrate placement of the therapy transducer to arrive at each survey point.
In some aspects, the method comprises displaying on a user interface the automated treatment plan, wherein the automated treatment plan defines one or more of a volume to be treated a depth of plan, and a margin.
In one aspect, a user interface displays an indication of treatment each focal location of the planned treatment volume following application of histotripsy pulses to the focal location.
In some aspects, the user interface displays an indication of which focal locations in the planned treatment volume is currently receiving histotripsy pulses.
In one aspect, the method includes a user interface displaying an ultrasound image acquired by an ultrasound imaging transducer, the ultrasound image depicting at least a portion of the planned treatment volume.
In some aspects, upon application of the histotripsy pulses the bubble cloud is viewable in the ultrasound image.
In one aspect, the method further comprises depicting one or more of a focal point, the planned treatment volume, a margin, or an acoustic field of the therapy transducer on the ultrasound image.
In some aspects, ultrasound imaging continues throughout the automatic treatment plan such that visualization of histotripsy pulses to each focal location is visualized.
In one aspect, the ultrasound images are fused ultrasound images depicted in combination with preprocedural image sets.
In some aspects, the method further comprises detecting a resistance to movement of the therapy transducer and displaying an indicator of the resistance on a user interface.
A method of fusing images is provided comprising: navigating a combined imaging and treatment transducer assembly to a location on a patient enabling visualization of a region of interest; performing an ultrasound sweep using the imaging transducer of the combined imaging and treatment transducer assembly to capture a volume of ultrasound images; marking a registration point in an ultrasound image from the ultrasound sweep, marking a registration point in an image from a preprocedural image set; fusing the preprocedural image set with the ultrasound images from the ultrasound sweep to form fused images; reviewing fused images; accepting a fusion, an displaying on a user interface live ultrasound images fused with the preprocedural image set.
In one aspect, the method includes verifying the combined imaging and therapy transducer assembly is approximately centered over the region of interest in multiple planes.
In some aspects, the method comprises marking a plurality of registration points in images from the ultrasound sweep and a plurality of registration points in the preprocedural image set.
In one aspect, the method further comprises initiating a breath hold of the patient prior to performing the ultrasound sweep.
In some aspects, the method comprises adjusting orientation and position of the combined imaging and therapy transducer assembly to optimize visualization of a region of interest with the imaging transducer.
In another aspect, the method comprises rotating the imaging transducer of the combined imaging and therapy transducer assembly 90 degrees to confirm visualization of the region of interest.
In some aspects, the method comprises displaying the ultrasound images captured during the ultrasound sweep.
In one aspect, the method comprises editing the ultrasound images captured during the ultrasound sweep.
In some aspects, the images remaining after editing of the images are only those images depicting a region of interest.
In another aspect, the registration point placed in the ultrasound images corresponds to the registration point in the preprocedural image set and are placed at an anatomical landmark appearing in both the ultrasound image and the preprocedural image set.
In some aspects, the method comprises determining whether sufficient anatomical landmarks have been identified in the ultrasound image and the preprocedural image set.
In another aspect, the system comprises placing at least one registration point in a plurality of ultrasound images, and at least one registration point in multiple images of the preprocedural image set.
In some aspects, the method includes adjusting a position of the registration point in the ultrasound image or a position of the registration point in the preprocedural image set.
In some aspects, the method includes adjusting the registration of the images from the ultrasound sweep with the preprocedural image set by dragging or rotating at least one image of the preprocedural image set relative to an image of the ultrasound sweep.
In other aspects, the method comprises verifying an alignment of anatomy of the patient in the live ultrasound images and the preprocedural image set.
In one aspect, the method includes rotating the imaging transducer of the combined imaging and therapy transducer assembly 90 degrees to verify the alignment.
In another aspect, the method includes adjusting the displayed live ultrasound images fused with the preprocedural image set.
A system is also provided that is configured for use according to method claims described above.
A method of planning a histotripsy therapy is provided comprising: visualizing a target treatment volume with an ultrasound imaging system in a first plane; displaying a target contour around the treatment volume in an ultrasound image generated by the ultrasound imaging system; adjusting the target contour around the treatment volume in the first plane; confirm that an acoustic pathway of a therapy transducer is substantially free of obstructions in the first plane; visualizing the target treatment volume with the ultrasound imaging system in a second plane; displaying the target contour around the treatment volume in a second ultrasound image generated by the ultrasound imaging system; adjusting the target contour around the treatment volume in the second plane; and confirm that the acoustic pathway of the therapy transducer is substantially free of obstructions in the second plane.
In some aspects, the target contour in the first plane and the target contour in the second plane define a volume for treatment.
In another aspect, the method includes displaying a margin around the treatment volume.
In some aspects, the method comprises defining a plurality of survey points of the treatment volume.
In some aspects, the survey points are located at a center of the treatment volume and at points along three orthogonal axes extending outward from the center of the treatment volume where the axes intersect the margin.
In one aspect, the axes are X, Y, and Z.
In other aspects, the first plane is an YZ plane.
In some aspects, the second plane is an XZ plane.
In another aspect, adjusting the target contour in the first plane defines a diameter of the treatment volume along the Y axis and a diameter of the treatment volume along the Z axis.
In some aspects, the method comprises confirming the target contour in the first plane is centered in the YZ plane and the target contour in the second plane is centered in the XZ plane.
In one aspect, the method comprises receiving a selection of one of the survey points.
In some aspects, the method comprises robotically driving the therapy transducer to the selected survey point.
In some aspects, the method further comprises detecting resistance to movement of the therapy transducer while moving to the selected survey point.
In some aspects, if a value of the detected resistance exceeds a threshold an indicator or the threshold is depicted.
In another aspect, the method includes detecting whether a value of resistance exceeds a second threshold and stopping robotic movement of the therapy transducer.
In one aspect, the method further comprises adjusting one of target contour or margin of the treatment volume or focal point of the therapy transducer and driving to the survey point.
In some aspects, the method comprises receiving confirmation that all survey points have been driven to.
In another aspect, the method includes receiving via a user interface an indication of a location of an intersection of a muscle layer and a fat layer.
In some aspects, the method comprises receiving a verification that the treatment volume is within the target contour in the first plane and the target contour in the second plane throughout a breathing cycle.
In some aspects, a coupling medium level in a coupling container in which a therapy transducer is located is sufficient to ensure ultrasound coupling at all survey points.
This disclosure is directed to systems and methods for histotripsy and histotripsy systems In accordance with the disclosure, one aspect is directed to systems and methods of confirming placement of a treatment head assembly including a focused ultrasound therapy transducer (e.g., histotripsy therapy transducer) exterior to the patient and positioned in alignment with a region of interest comprising target tissue and a planned treatment volume. In some embodiments, the system is configured with features to aid in localizing, targeting, and verifying that the target tissue within the planned treatment volume is visible under ultrasound images prior to commencement of the therapy delivery phases of the procedure In other embodiments, tracked ultrasound imaging may be used to register secondary imaging modalities (e.g., CT, MRI, CBCT, contrast enhanced ultrasound, etc.) with the live ultrasound images to further enrich the visualization of region of interest and target tissue. By these methods, the systems described herein can be placed and configured such that energy obstruction or absorption by tissues (e.g., bone or bowel gas) is minimized or avoided thus reducing the energy required for initiating or maintaining histotripsy therapy as well as mitigating injury to prefocal and intervening tissue. In addition, forces applied to the patient or to a therapy assembly is measured, monitored, and reacted to (if needed) to maintain acceptable safety levels throughout the duration of the procedure. These system features are designed to ensure the safety of the patient, system and system components are maintained. In addition, these system features ensure that the anatomy, organs and other soft tissues of interest are not moved or altered in an unacceptable way during the procedure. Further, based on unique and heterogeneous patient specific treatment scenario(s) given the varied location, size, and tissue pathway to targeted tissue locations, and patient specific variables (body mass index, anatomy, etc.), an in situ treatment plan is developed for a user defined 3D planned treatment volume ensuring complete therapy is delivered to the treatment volume, including a user defined margin, and as delivered using a specific treatment pattern and pathway as the system moves through the plan and delivers one or more histotripsy pulse sequences at one or more treatment zones and defined focal locations.
Histotripsy comprises short, high amplitude, focused ultrasound pulses to generate a dense, energetic, “bubble cloud,” capable of the targeted fractionation and destruction of tissue. Histotripsy is capable of creating controlled tissue erosion when directed at a tissue interface, including tissue/fluid interfaces, as well as well-demarcated tissue fractionation and destruction, at sub-cellular levels, when it is targeted at bulk tissue. Unlike other forms of ablation, including thermal and radiation-based modalities, histotripsy does not rely on heat or ionizing (high) energy to treat tissue. Instead, histotripsy uses acoustic cavitation generated at the focus to mechanically effect tissue structure, and in some cases liquefy, suspend, solubilize and/or destruct tissue into sub-cellular components.
Histotripsy can be applied in various forms, including: 1) Intrinsic-Threshold Histotripsy: Delivers pulses with at least a single negative/tensile phase sufficient to cause a cluster of bubble nuclei intrinsic to the medium to undergo inertial cavitation, 2) Shock-Scattering Histotripsy: Delivers pulses of about 3-20 cycles in duration. The amplitude of the tensile phases of the pulses is sufficient to cause bubble nuclei in the medium to undergo inertial cavitation within the focal zone throughout the duration of the pulse. These nuclei scatter the incident shockwaves, which invert and constructively interfere with the incident wave to exceed the threshold for intrinsic nucleation, and 3) Boiling Histotripsy; Employs pulses roughly 1-20 ms in duration. Absorption of the shocked pulse rapidly heats the medium, thereby reducing the threshold for intrinsic nuclei. Once this intrinsic threshold coincides with the peak negative pressure of the incident wave, boiling bubbles form at the focus.
The large pressure generated at the focus causes a cloud of acoustic cavitation bubbles to form above certain thresholds, which creates localized stress and strain in the tissue and mechanical breakdown without significant heat deposition. At pressure levels where cavitation is not generated, minimal effect is observed on the tissue at the focus. This cavitation effect is observed only at pressure levels significantly greater than those which define the inertial cavitation threshold in water for similar pulse durations, on the order of 10 to 30 MPa peak negative pressure.
Histotripsy may be performed in multiple ways and under different parameters. It may be performed totally non-invasively by acoustically coupling a focused ultrasound transducer over the skin of a patient and transmitting acoustic pulses transcutaneously through overlying (and intervening) media and tissue to the focal zone (treatment zone and site). It may be further targeted, planned, directed and observed under direct visualization, via ultrasound imaging, given the bubble clouds generated by histotripsy may be visible as highly dynamic, echogenic regions on, for example, B Mode ultrasound images, allowing continuous visualization through its use (and related procedures). Likewise, the treated and fractionated tissue shows a dynamic change in echogenicity (typically a reduction), which can be used to evaluate, plan, observe and monitor treatment.
Generally, in histotripsy treatments, ultrasound pulses with 1 or more acoustic cycles are applied, and the bubble cloud formation relies on the pressure release scattering of the positive shock fronts (sometimes exceeding 100 MPa, P+) from initially initiated, sparsely distributed bubbles (or a single bubble). This is referred to as the “shock scattering mechanism”.
This mechanism depends on one (or a few sparsely distributed) bubble(s) initiated with the initial negative half cycle(s) of the pulse at the focus of the transducer. A cloud of microbubbles then forms due to the pressure release backscattering of the high peak positive shock fronts from these sparsely initiated bubbles. These back-scattered high-amplitude rarefactional waves exceed the intrinsic threshold thus producing a localized dense bubble cloud. Each of the following acoustic cycles then induces further cavitation by the backscattering from the bubble cloud surface, which grows towards the transducer. As a result, an elongated dense bubble cloud growing along the acoustic axis opposite the ultrasound propagation direction is observed with the shock scattering mechanism. This shock scattering process makes the bubble cloud generation not only dependent on the peak negative pressure, but also the number of acoustic cycles and the amplitudes of the positive shocks. Without at least one intense shock front developed by nonlinear propagation, no dense bubble clouds are generated when the peak negative half-cycles are below the intrinsic threshold.
When ultrasound pulses less than 2 cycles are applied, shock scattering can be minimized, and the generation of a dense bubble cloud depends on the negative half cycle(s) of the applied ultrasound pulses exceeding an “intrinsic threshold” of the medium. This is referred to as the “intrinsic threshold mechanism”.
This threshold can be in the range of 26-30 MPa for soft tissues with high water content, such as tissues in the human body. In some embodiments, using this intrinsic threshold mechanism, the spatial extent of the lesion may be well-defined and more predictable with peak negative pressures (P−) not significantly higher than this threshold, sub-wavelength reproducible lesions as small as half of the −6 dB beam width of a transducer may be generated.
With high-frequency Histotripsy pulses, the size of the smallest reproducible lesion becomes smaller, which is beneficial in applications that require precise lesion generation. However, high-frequency pulses are more susceptible to attenuation and aberration, rendering problematical treatments at a larger penetration depth (e.g., ablation deep in the body) or through a highly aberrative medium (e.g., transcranial procedures, or procedures in which the pulses are transmitted through bone(s)) Histotripsy may further also be applied as a low-frequency “pump” pulse (typically <2 cycles and having a frequency between 100 kHz and 1 MHz) can be applied together with a high-frequency “probe” pulse (typically <2 cycles and having a frequency greater than 2 MHz, or ranging between 2 MHz and 10 MHz) wherein the peak negative pressures of the low and high-frequency pulses constructively interfere to exceed the intrinsic threshold in the target tissue or medium. The low-frequency pulse, which is more resistant to attenuation and aberration, can raise the peak negative pressure P− level for a region of interest (ROI), while the high-frequency pulse, which provides more precision, can pin-point a targeted location within the ROI and raise the peak negative pressure P− above the intrinsic threshold. This approach may be referred to as “dual frequency”, “dual beam histotripsy” or “parametric histotripsy.”
Additional systems, methods and parameters to deliver optimized histotripsy, using shock scattering, intrinsic threshold, and various parameters enabling frequency compounding and bubble manipulation, are herein included as part of the system and methods disclosed herein, including additional means of controlling said histotripsy effect as pertains to steering and positioning the focus, and concurrently managing tissue effects (e.g., prefocal thermal collateral damage) at the treatment site or within intervening tissue. Further, it is disclosed that the various systems and methods, which may include a plurality of parameters, such as but not limited to, frequency, operating frequency, center frequency, pulse repetition frequency, pulses, bursts, number of pulses, cycles, length of pulses, amplitude of pulses, pulse period, delays, burst repetition frequency, sets of the former, loops of multiple sets, loops of multiple and/or different sets, sets of loops, and various combinations or permutations of, etc., are included as a part of this disclosure, including future envisioned embodiments of such. This further includes the ability to vary these parameters, spatially and temporally, throughout treatments and treatment plans.
The disclosed system may comprise various imaging modalities to allow users to visualize, monitor and collect/use feedback of the patient's anatomy, related regions of interest and treatment/procedure sites, as well as surrounding and intervening tissues to assess, plan and conduct procedures, and adjust treatment parameters as needed. Imaging modalities may comprise various ultrasound, x-ray, CT, MRI, PET, fluoroscopy, optical, contrast or agent enhanced versions, and/or various combinations of. It is further disclosed that various image processing and characterization technologies may also be utilized to afford enhanced visualization and user decision making. These may be selected or commanded manually by the user or in an automated fashion by the system. The system may be configured to allow side by side, toggling, overlays, 3D reconstruction, segmentation, registration, multi-modal image fusion, image flow, and/or any methodology affording the user to identify, define and inform various aspects of using imaging during the procedure, as displayed in the various system user interfaces and displays Examples may include locating, displaying and characterizing regions of interest, organ systems, potential treatment sites within, with on and/or surrounding organs or tissues, identifying critical structures such as ducts, vessels, nerves, ureters, fissures, capsules, tumors, tissue trauma/injury/disease, other organs, connective tissues, etc., and/or in context to one another, of one or more (e.g., tumor draining lymphatics or vasculature; or tumor proximity to organ capsule or underlying other organ), as unlimited examples.
Systems may be configured to include onboard integrated imaging hardware, software, sensors, probes and wetware, and/or may be configured to communicate and interface with external imaging and image processing systems. The aforementioned components may be also integrated into components wherein probes, imaging arrays, or the like, and electrically, mechanically or electromechanically integrated into therapy transducers. This may afford, in part, the ability to have geometrically aligned imaging and therapy, with the therapy directly within the field of view, and in some cases in line, with imaging. In some embodiments, this integration may comprise a fixed orientation of the imaging capability (e.g., imaging probe) in context to the therapy transducer. In other embodiments, the imaging solution may be able to move or adjust its position, including modifying angle, extension (e.g., distance from therapy transducer or patient), rotation (e.g., imaging plane in example of an ultrasound probe) and/or other parameters, including moving/adjusting dynamically while actively imaging. The imaging component or probe may be encoded so its orientation and position relative to another aspect of the system, such as the therapy transducer, and/or robotically-enabled positioning component may be determined. Additionally, the imaging component or probe may be co-registered to the robotic system to accurately locate/display the focus of the therapy system in the context of images from one or more imaging components or probes.
In one embodiment, the system may comprise onboard ultrasound, further configured to allow users to visualize, monitor and receive feedback for procedure sites through the system displays and software, including allowing ultrasound imaging and characterization (and various forms of), ultrasound guided planning and ultrasound guided treatment, all in real-time. The system may be configured to allow users to manually, semi-automatically, or fully automatically image the patient (e.g., by hand or using a robotically-enabled imager). In some embodiments, the robotic system can sweep the onboard ultrasound system (e.g., linear and/or angular sweeps) across a target volume to generate volumetric imaging data.
The user may be allowed to further select, annotate, mark, highlight, and/or contour, various regions of interest or treatment sites, and defined treatment targets (on the image(s)), of which may be used to command and direct the system where to image, test and/or treat, through the system software and user interfaces and displays In some arrangements, the user may use a manual ultrasound probe (e.g., diagnostic hand-held probe) to conduct the procedure. In another arrangement, the system may use a robot and/or electromechanical positioning system to conduct the procedure, as directed and/or automated by the system, or conversely, the system can enable combinations of manual and automated uses. The system may also various settings or modes of viewing visualization features (e.g., marks, contours, and/or other overlays) including toggling them on and/or off, etc.
The system may further include the ability to conduct image registration, including imaging and image data set registration to allow navigation and localization of the system to the patient, including the treatment site (e.g., tumor, critical structure, bony anatomy, anatomy and identifying features of, etc.). In one aspect, the system allows the user to image and identify a region of interest, for example the liver, using integrated ultrasound, and to select and mark a tumor (or surrogate marker of) comprised within the liver through/displayed in the system software, and wherein said system registers the image data to a coordinate system defined by the system, that further allows the system's therapy and robotics components to deliver synchronized acoustic cavitation/histotripsy to said marked tumor. The system may comprise the ability to register various image sets, including those previously disclosed, to one another, as well as to afford navigation and localization (e.g., of a therapy transducer to a CT or MRI/ultrasound fusion image with the therapy transducer and robotics components tracking to said image).
The system may also comprise the ability to work in a variety of interventional, endoscopic and surgical environments, including alone and with other systems (surgical/laparoscopic towers, vision systems, endoscope systems and towers, ultrasound enabled endoscopic ultrasound (flexible and rigid), percutaneous/endoscopic/laparoscopic and minimally invasive navigation systems (e.g., optical, electromagnetic, shape-sensing, ultrasound-enabled, etc.), of also which may work with, or comprise various optical imaging capabilities (e.g., fiber and or digital). The disclosed system may be configured to work with these systems, in some embodiments working alongside them in concert, or in other embodiments where all or some of the system may be integrated into the above systems/platforms (e.g., acoustic cavitation/histotripsy-enabled endoscope system or laparoscopic surgical robot). In many of these environments, a therapy transducer may be utilized at or around the time of use, for example, of an optically guided endoscope/bronchoscope, or as another example, at the time a laparoscopic robot (e.g., Intuitive Da Vinci multi and single port systems) is viewing/manipulating a tissue/treatment site. Further, these embodiments and examples may include where said other systems/platforms are used to deliver (locally) fluid to enable the creation of a man-made acoustic window, where on under normal circumstances may not exist (e.g., fluidizing a segment or lobe of the lung in preparation for acoustic cavitation/histotripsy via non-invasive transthoracic treatment (e.g., transducer externally placed on/around patient). Components disclosed herein may also comprise all or some of their component hardware packaged within the other system (e.g., cart, computing device, memory, etc.).
The system may also be configured, through various aforementioned parameters and other parameters, to display real-time visualization of a bubble cloud in a spatial-temporal manner, including the resulting tissue effect peri- or post-treatment from tissue to bubble cloud interaction, wherein the system can dynamically image and visualize, and display, the bubble cloud, and any changes to it (e.g., decreasing or increasing echogenicity), which may include intensity, shape, size, location, morphology, persistence, etc. These features may allow users to continuously track and follow the treatment in real-time in one integrated procedure and interface/system, and confirm treatment safety and efficacy on the fly (versus other interventional or surgical modalities, which either require multiple procedures to achieve the same, or where the treatment effect is not visible in real-time (e.g., radiation therapy), or where it is not possible to achieve such (e.g., real-time visualization of local tissue during thermal ablation), or where the other procedure further require invasive approaches (e.g., incisions or punctures) and iterative imaging in a scanner between procedure steps (e.g., CT or MRI scanning). The above components, modalities, features and work-flows and methods of use may be implemented in an unlimited fashion through enabling hardware, software, user interfaces and use environments, and future improvements, enhancements and inventions in this area are considered as included in the scope of this disclosure, as well as any of the resulting data and means of using said data for analytics, artificial intelligence or digital health applications and systems.
The system may comprise various software applications, features and components which allow the user to interact, control and use the system for a plethora of clinical applications. The Software may communicate and work with one or more of the components including but not limited to therapy, integrated imaging, robotics and other components, ancillaries and accessories of the system.
Overall, in no specific order of importance, the software may provide features and support to initialize and set up the system, service the system, communicate and import/export/store data, modify/manipulate/configure/control/command various settings and parameters by the user, mitigate safety and use-related risks, plan procedures, provide support to various configurations of transducers, robotic arms and drive systems, function generators and amplifier circuits/slaves, test and treatment ultrasound sequences, transducer steering and positioning (electromechanical and electronic beam steering, etc.), treatment patterns, support for imaging and imaging probes, manual and electromechanical/robotically-enabling movement of, imaging support for measuring/characterizing various dimensions within or around procedure and treatment sites (e.g., depth from one anatomical location to another, etc., pre-treatment assessments and protocols for measuring/characterizing in situ treatment site properties and conditions (e.g., acoustic cavitation/histotripsy thresholds and heterogeneity of), targeting and target alignment, calibration, marking/annotating, localizing/navigating, registering, guiding, providing and guiding through work-flows, procedure steps, executing treatment plans and protocols autonomously, autonomously and while under direct observation and viewing with real-time imaging as displayed through the software, including various views and viewports for viewing, communication tools (video, audio, sharing, etc.), troubleshooting, providing directions, warnings, alerts, and/or allowing communication through various networking devices and protocols. It is further envisioned that the software user interfaces and supporting displays may comprise various buttons, commands, icons, graphics, text, etc., that allow the user to interact with the system in a user-friendly and effective manner, and these may be presented in an unlimited number of permutations, layouts and designs, and displayed in similar or different manners or feature sets for systems that may comprise more than one display (e.g., touch screen monitor and touch pad), and/or may network to one or more external displays or systems (e.g., another robot, navigation system, system tower, console, monitor, touch display, mobile device, tablet, etc.).
The software, as a part of a representative system, including one or more computer processors, may support the various aforementioned function generators (e.g., FPGA), amplifiers, power supplies and therapy transducers. The software may be configured to allow users to select, determine and monitor various parameters and settings for acoustic cavitation/histotripsy, and upon observing/receiving feedback on performance and conditions, may allow the user to stop/start/modify said parameters and settings.
The software may be configured to allow users to select from a list or menu of multiple transducers and support the auto-detection of said transducers upon connection to the system (and verification of the appropriate sequence and parameter settings based on selected application). In other embodiments, the software may update the targeting and amplifier settings (e.g., channels) based on the specific transducer selection. The software may also provide transducer recommendations based on pre-treatment and planning inputs. Conversely, the software may provide error messages or warnings to the user if said therapy transducer, amplifier and/or function generator selections or parameters are erroneous, yield a fault or failure. This may further comprise reporting the details and location of such.
In addition to above, the software may be configured to allow users to select treatment sequences and protocols from a list or menu, and to store selected and/or previous selected sequences and protocols as associated with specific clinical uses or patient profiles. Related profiles may comprise any associated patient, procedure, clinical and/or engineering data, and may be used to inform, modify and/or guide current or future treatments or procedures/interventions, whether as decision support or an active part of a procedure itself (e.g., using serial data sets to build and guide new treatments).
As a part of planning or during the treatment, the software (and in working with other components of the system) may allow the user to evaluate and test acoustic cavitation/histotripsy thresholds at various locations in a user-selected region of interest or defined treatment area/volume, to determine the minimum cavitation thresholds throughout said region or area/volume, to ensure treatment parameters are optimized to achieve, maintain and dynamically control acoustic cavitation/histotripsy In one embodiment, the system allows a user to manually evaluate and test threshold parameters at various points. The threshold points may include those at defined boundary, interior to the boundary and center locations/positions, of the selected region of interest and treatment area/volume, and where resulting threshold measurements may be reported/displayed to the user, as well as utilized to update therapy parameters before treatment. In another embodiment, the system may be configured to allow automated threshold measurements and updates, as enabled by the robotics components, wherein the user may direct the robot, or the robot may be commanded to execute the measurements autonomously.
Software may also be configured, by working with computer processors and one or more function generators, amplifiers and therapy transducers, to allow various permutations of delivering and positioning optimized acoustic cavitation/histotripsy in and through a selected area/volume. This may include, but not limited to, systems configured with a fixed/natural focus arrangement using purely electromechanical positioning configuration(s), electronic beam steering (with or without electromechanical positioning), electronic beam steering to a new selected fixed focus with further electromechanical positioning, axial (Z axis) electronic beam steering with lateral (X and Y) electromechanical positioning, high speed axial electronic beam steering with lateral electromechanical positioning, high speed beam steering in 3D space, various combinations of including with dynamically varying one or more acoustic cavitation/histotripsy parameters based on the aforementioned ability to update treatment parameters based on threshold measurements (e.g., dynamically adjusting amplitude across the treatment area/volume).
A variety of treatment patterns and pathways may be utilized to position the bubble cloud in one or more desired focal locations within a target tissue volume as part of a treatment plan. Patterns may comprise one or more focal locations of specified location in 2D and 3D space, including configurable pattern variables including, but not limited to, the location, spacing, and/or defined overlap (minimum and/or maximum) of focal locations. This may further include the groupings of focal locations into various desired shapes (e.g., columns, ellipses, layers, etc.), wherein the shapes can be packed/placed into a larger volume. For example, an ellipsoidal volume comprised of radial layers (of packed focal locations) or in contrast, an ellipsoidal volume comprised of rectilinear columns. Patterns may comprise unlimited features and variations when considering the size of the treatment volume, bubble cloud configuration (size) and position (placement of the bubble cloud/focal location) in a treatment volume (centered, off-center, similar or varied center to center alignment/orientation, etc.).
In terms of “pathways”, these may comprise various techniques for motioning and moving the bubble cloud through the selected or defined pattern. In some embodiments, this may comprise moving to the next nearest point in the pattern. In other embodiments, it may comprise moving to a preferred position in the plan that is at a distance from the current focal location (e.g., two or more focal locations away) In some configurations, the pathway may comprise moving to the farthest focal location. Pathways may be configurable based on, for example, desired cooling profiles.
In some embodiments and system configurations, this may include a linear pattern and pathway that traverses a spherical treatment volume in a series of axial slices (parallel to the imaging plane), beginning with the center slice within the treatment volume and progressing outward in the positive x-dimension (relative to the transducer array) until the entire +x-half of the spherical treatment volume is treated. The treatment then moves to the untreated slice adjacent to the center and treats the remaining half of the spherical volume in an analogous manner, in this case progressing outward in the negative x-dimension within each slice, treatment may start at the center point and moves outward in a spiraling fashion.
A “Top-Down” and “Bottom-Up” patterns and pathways differ from other rectilinear patterns in that they do not traverse the treatment volume in axial slices; rather, the robotic system is configured to move the transducer array focus to progress through the treatment volume in a series of lateral slices (i.e., slices perpendicular to the acoustic axis of the therapy transducer). Within each slice, treatment starts at the center point and moves outward in a spiraling fashion (identical to the manner in which a representative rectilinear pattern traverses an axial slice). As the names imply, the “Top-Down” and “Bottom-Up” patterns progress through the lateral planes of the sphere from the upper-most (closest to the transducer) to the distal-most (farthest from the transducer) or distal-most to upper-most, respectively.
In another configuration, the pattern and pathway may comprise a target tissue volume that is divided into a number of slices, which are treated in alternating order starting from the middle of the volume (number below each slice indicates treatment order). Within each slice columns are treated in an alternating fashion (number below each column indicates treatment order). The columns themselves can be traversed in a top-down or a bottom-up manner, and/or combination of, depending on the treatment type, tissue, type, and tissue location.
Other patterns and pathways may represent variations of these patterns In one example, the spherical volume is still traversed in a set of axial slices parallel to the imaging plane, and the progression of treatment within each slice remains the same. Only the order in which the axial slices are treated is varied in these two schemes. Specifically, in one embodiment, pattern and pathway treats the axial slices starting at one lateral extreme of the volume (e.g., the slice farthest in the +x-dimension) and progresses through slices one at a time until reaching the other lateral extreme of the volume (the slice farthest in the −x-dimension). In another configuration, the pattern and pathway increments through slices in a strategic order selected to maximize the spatial distribution/distance of successive treatment slices. If the center axial slice of the sphere is defined as slice 0, the slice farthest in the +x-dimension as 6, and the slice farthest in the −x-dimension as −6, then in this example, treatment progresses through the 13 slices comprising the 3 cm sphere in the following order: 0, 4, −2, −5, −1, 6, −3, 5, 1, −6, 3, −4, 2.
In one “Spiral In-Out” pattern and pathway example, treatment occurs by traversal through the spherical volume in a series of radial layers, from the center of the sphere outward. Within each layer, and when transitioning between layers, the points are treated in order of proximity (i.e., the next treatment point is the closest untreated point in the current radial layer, or the closest point in the next radial layer when transitioning between layers). In some embodiments, the pattern can move in a spiral or circular movement throughout each layer. When a given layer is completed, the pattern can transition to the next layer, typically the closest layer in the given propagation direction. The spiral patterns described herein can treat from the distal most layer to the proximal most layer (respective to the transducer) or vis versa.
Combinations of pattern and pathway traversal are also included. In particular, combinations of the “Spiral In-Out” and “Bottom-up” are envisioned, wherein the distal-most layer is treated first in a pattern spiraling generally outward, from an interior treatment point. Transitioning between layers in a distal to proximal fashion, while generally treating an interior treatment point initially within each new layer, before progressing to the outward treatment points.
In other examples, the size of the cavitation or bubble cloud at a given focal location can be increased or enhanced with rapid electronic steering techniques that rapidly steer between multiple points at or intersecting with a given focal location. This technique can be referred to herein as “bubble saber”. The “bubble saber” or column shape end effector can be implemented by rapidly electronically steering the bubble cloud focus in any direction (e.g., in the z-direction, in the x-y direction, in 3D space) through an enhanced volume of treatment points and defined steering distance, and optionally repeating the rapid electronic steering multiple times. In some embodiments, this configuration may enable the user to manipulate the bubble saber position via the robot and software to treat a defined treatment area. This may include treating tissue for the application of creating a treatment plane (across an organ and/or anatomic structure, e.g., a fissure, an organ segment boundary, and/or a desired resection plane, etc.). In some cases, this may be enabled as a linear end-effector (z-axis only). In other configurations, including those enabling 3D electronic steering, the end-effector may include non-linear shapes (e.g., arc).
The “bubble saber” technique can also provide a large thermal benefit by electronically steering the bubble cloud to a more proximal location than the geometric focus to ablate shallower targets. The primary thermal benefit of the “bubble saber” technique comes from the electronic steering itself (utilization of the lowest possible effective f number). Another benefit of the “bubble saber” is the reduced impact of motion on local dose, and the potential efficacy benefits of a more parallel treatment strategy (providing some protection against untreated volumes of tissue moving or shifting to a previously treated area as a result of treatment in surrounding areas and thereby escaping further treatment). In some embodiments, the “bubble saber” may comprise a linear end-effector, in in some configurations, it may comprise an arc or curved end-effector, based on the desired treatment plan/plane.
In another embodiment, histotripsy therapy can be applied in a “radial spiral” pattern that minimizes the distance between treatment columns while maintaining an “inside-out” lesion development in tissue instead of columns of treatment points arranged in a cartesian grid of locations, the treatment points in this technique are arranged in radial layers. These layers are then treated from inside out, with columns within each layer treated sequentially around each ring in a spiral (or alternating from side to side if preserving the thermal benefit of sequential treatment columns being are distant as possible is required). This pattern provides a more consistent cloud overlap in three-dimensions and minimized the distance between successive treatment columns compared to a rectilinear treatment pattern, resulting in a planned ablation volume that more closely matches ellipsoidal planning contours.
The radial spiral technique allows the flexibility to reduce treatment times by removing the de facto cooling time when moving between spatially distant treatment columns. Though that this pattern does not remove the need for this cooling time, it allows the flexibility to include or exclude cooling time only as required by the anticipated thermal load, i.e., the option to go faster if thermally tolerable. The radial spiral may proceed in a clock-wise or counter-clockwise direction.
A planned bubble cloud treatment treats a specified percentage of the target tissue volume. In some examples, it is desirable for a chosen pattern to cover completely or nearly the entire tissue volume. In some embodiments, the pattern can be implemented to cover 90-100% of the target tissue volume. In other examples, it may be desirable to treat only 50% or less of a given volume. The amount or percentage of treatment may depend on the tissue type, tissue location, etc. Focal location center points for each bubble cloud may be distributed at discrete spacing in X and Y, with any points outside the tissue volume boundary discarded. Point positions in Z may also be dynamically adjusted to match the tissue volume boundary contour. The spacing between adjacent focal locations may be adjusted to determine the amount, if any, of overlap between focal locations. In one example, focal location center points for each bubble cloud may be distributed in radial layers in X and Y, with radii dynamically adjusted to match the target tissue volume boundaries. Focal location positions in Z may also dynamically adjusted to match the target tissue volume boundary contours.
As described above, the systems described herein include the capability to evaluate and test acoustic cavitation/histotripsy thresholds at various locations in a user-selected region of interest or defined treatment area/volume, to determine the minimum cavitation thresholds throughout said region or area/volume, to ensure treatment parameters are optimized to achieve, maintain and dynamically control acoustic cavitation/histotripsy. During treatment planning or during therapy, cavitation threshold test pulses can be transmitted into a plurality of locations of interest. The number of test locations of interest can be chosen based on the size and/or shape of the treatment region. For example, in a spherical treatment region benefits from at least seven test locations to probe the extremes of the spherical volume, these may include the center of the treatment area or treatment volume and axes end points where each of the X. Y and Z axes intersect the boundary of the treatment area or treatment volume.
During therapy, the cavitation threshold at each of the locations of interest can be evaluated with a test series of pulses at an initial driving voltage and pulse repetition frequency (PRF) to determine if cavitation has formed before incrementing the driving voltage or to the next PRF. PRF may be defined as the number of pulses delivered every second by the systems described herein. PRF can be adjusted during therapy depending on the cavitation threshold, the tissue type, depth, etc. The formation (or not) of cavitation can be observed in real-time with imaging such as ultrasound imaging. In general, the driving voltage required to initiate a vigorous bubble cloud in tissue decreases as the PRF increases. The cavitation threshold in the tissue can also vary as a treatment procedure progresses. Thus, testing various points of interest within a treatment volume for treatment can be a useful tool to evaluate the cavitation threshold(s) and adjust the PRF or driving voltage of the therapy pulses to optimize treatment at each of the tested locations. The treatment protocol itself can then be adjusted based on the test pulses to utilize variable driving voltages or PRF based on the test results to ensure the optimal amount of energy is delivered into each location of the tissue for histotripsy therapy. Additionally, the depth at each of the test locations can be measured or determined (either manually or automatically with the system) to provide additional information to the system for determining optimal treatment parameters.
In some embodiments, the test locations can be used to determine a maximum amount of energy that may be applied without generating undesired damage to the test location or surround or intervening tissues. For example, while determining the cavitation thresholds at each of the test locations, the drive voltage or PRF of the system can be increased until cavitation is observed under real-time imaging and/or other feedback mechanisms. In some embodiments, the drive voltage or PRF can be increased until undesirable damage to the test location or cavitation or thermal damage to other locations outside of the test location are observed. This can be used to determine the maximum amount of energy that can be applied for a given test location.
Based on the test protocol and tested cavitation thresholds, the appropriate driving voltage for each point in the treatment grid can be chosen. With the required voltage at the center and six extremes of the target volume serving as inputs, the voltages for the remaining points comprising the treatment volume can be interpolated. The driving voltage can then be adjusted automatically by the software as the therapy progresses through the automated treatment volume. In this way each point is ablated using an amplitude sufficient to maintain an efficacious bubble cloud, but not overly so in order to minimize the thermal deposition in the acoustic path.
For example, a method of delivering histotripsy therapy to tissue can comprise delivering histotripsy pulses into tissue at a plurality of target test locations and imaging the test location in real-time to evaluate whether cavitation has formed at the test locations. If cavitation has not formed at the test locations, the driving voltage or the PRF of the histotripsy pulses can be adjusted, and histotripsy pulses with the adjusted parameters can be delivered into the tissue at the test locations. Real-time imaging can again be used to evaluate whether cavitation has formed at each test location. This process can be repeated until the cavitation threshold at each test location is determined, and a high-density map can be created based on various algorithms to extrapolate thresholds across the targeted region of interest/treatment volume, specific to the acoustic pathway and target depth. For example, if cavitation thresholds are known at a first test location and a second test location, then the cavitation threshold at a third test location can be extrapolated based on the cavitation thresholds of the first and second test locations. This extrapolation can be further based on the tissue type, target tissue depth, and acoustic pathway of the third test location.
A given Histotripsy therapy or treatment session can be defined in terms of a set number of pulses N that are to be delivered over a set total treatment time T. Thus, the total number of pulses N delivered over a total treatment time T (in seconds) is equal to the total treatment time T multiplied by the PRF of the system. For example, a system operating at a constant 200 Hz PRF for a total treatment time of 10 minutes (600 seconds) will have a total number of pulses N equal to 120,000. The systems and methods described herein can include PRF's of 400 Hz or greater to generate acoustic cavitation, including PRF's ranging from 400 to 900 Hz. As an example, if a PRF of 200 Hz is employed, therapy may be applied over 10 minutes.
Systems and methods are provided herein that implement Histotripsy pulse sequences with frequent short cooling periods that advantageously improve the thermal profile generated by histotripsy treatment, with the limiting case of N pulses equally distributed over the treatment time T yielding the minimum temperature rise. These pulse sequences can further be characterized in terms of the amount of time in which therapy is actively delivered to tissue relative to the amount of cooling time in which no therapy pulses are delivered to tissue. For example, a system delivering therapy pulses at a 400 Hz PRF for 5 minutes, followed by a 5 minute cooling time in which no therapy pulses are delivered (for a total treatment time of 10 minutes) would have a ratio of therapy (5 minutes) to cooling (5 minutes) of 1:1. PRF can be adjusted to any frequency between 200 and 900 Hz, and as frequency pf PRF is increased, greater and more frequent cessations of the application of energy can be employed. For example, at 400 Hz PRF, the therapy can be applied for 2.5 minutes followed by 2.5 minutes of cooling until a total of 10 minutes of therapy is achieved.
In general, when the therapy PRF is doubled and cooling steps are imposed the extent of the temperature rise is dependent on the distribution of cooling steps. A single long cooling step may result in the greatest temperature rise observed with this strategy. Conversely, shorter/more frequent cooling steps more closely approximate the case of equally distributed pulses and result in the lowest temperature rise observed with this strategy. Further, within a given total treatment time window, a higher therapy to cooling time ratio (e.g., 3:1) is generally advantageous to a lower therapy to cooling time ratio (e.g., 1:3). Essentially, for a set number of histotripsy pulses delivered within a given time window, a lower PRF is thermally beneficial.
Further details and examples relating to duration of therapy, PRF, therapy time, colling time, and other factors are described in detail in commonly assigned WO/2021258007 filed Jun. 18, 2021 entitled HISTOTRIPSY ACOUSTIC AND PATIENT COUPLING SYSTEMS AND METHODS, the entire contents of which is incorporated herein by reference.
When Histotripsy is used to ablate a target volume larger than the cavitation bubble clouds created by the system, the cavitation focus of the Histotripsy therapy system is moved (mechanically or electronically) within the target volume to ablate the entire target volume. In the context of this disclosure, mechanical movement can comprise movement of the physical position of the treatment head and/or therapy focus with the robotic positioning arm. Electronic movement of the focus, instead, is achieved with electronic-beam steering of the focus with the transducer array. In some embodiments, the focus can be electronically beam-steering without moving the physical position of the transducer array. In some embodiments, mechanical movement is combined with electronic beam-steering. This disclosure describes methods and workflows to and techniques to achieve a Histotripsy therapy.
The Histotripsy system 10 is configured for use with separate imaging systems, such as ultrasound, MRI, cone-beam CT, etc., to provide real-time and/or perioperative imaging during histotripsy therapy. As illustrated in
Having described the aspects of the workflow 50 at a high level each of these aspects will be described in greater detail starting with
Regardless of whether the treatment head 20 is attached, the user is directed to press and hold the ready position button 210 (
The selected treatment head (and associated identification data) may include embedded configuration information (and files) to be relayed or as inputs into the histotripsy system via hardware/software interfaces. In particular, a memory board inside transducer ZIF connector communicates with a ZIF board inside the generator. Other cables and forms of wireless communication may be used to share information between the various system components information can be passed between the transducer and the generator. System information which may be passed between the treatment head/therapy transducer and the rest of the system (e.g., generator) may include therapy transducer specification details including but not limited to model number, serial number, number of transducer elements, focal depth/length, thermal offset coefficients, element timing calibrations; indications of use (anatomical location, organ, disease, etc.); work-flow details including software pages to recall, use case details (e.g., ultrasound guided versus CBCT guided, etc.), payload, different therapy sequences, bubble cloud location, imaging plane calibration matrix, bubble cloud expected size, expected voltage to attain bubble cloud in water performance and total run time; and/or service related data including system check calibration data (if it has been calibrated in 24 hours/past calibration data), date of mfg, and hours until service due. Connection of the treatment head may also include connection of a ZIF cable to the cart/generator and other I/O connectors to one or more robotic arm configurations, and/or imaging systems (ultrasound, X-ray, etc.).
Once complete, and following selection of a next button 214, the UI 200 depicts the screen seen in
Following selection of the set-up complete button 218, the workflow moves into the system check phase (e.g., step 58 of
If a system check must be performed, step 114 is undertaken, where instructions are displayed in the UI 200 to fully extend the imaging probe 22 and to rotate the imaging probe 22 to the +X position. The actual position and orientation of the imaging probe 22 relative to the therapy transducer 18 is calculated continuously using signals sent via the I/O cable that can be interpreted by the software once the imaging probe 22 is moved to the required positions, as depicted by imaging probe orientation and position indicators 219, and the confirm button 220 is selected. When button 220 is selected, the software compares the actual signal for the position and orientation to a range of expected signals and the workflow will advance the UI 200 to the screen depicted in
Following selection of the confirm button 221 in the UI 200 of
As shown in
Following selection of a next button 224 in
Following set-up and system check the UI 200 progresses to the screen depicted in
Following selection of an image file and a next button 240 or selection of the skip import button 242 the UI 300 (
As shown in
Selection of the next button 324 advances the method 400 to a calibration phase 414 as depicted in
Selecting the next button 330 at the end of step 418 sets the reference point for the software application to calculate the buoyancy of the treatment head 20. Throughout the rest of the procedure, the buoyancy is subtracted from the force measured by the robotic arm in order to accurately determine real forces applied to the treatment head 20. As shown in
The buoyancy of the treatment head 20 is used to determine force applied to the treatment head 20 as a result of contact with the patient through the film or membrane 48. As will be appreciated, by driving the robotic arm 14, force can be applied by the treatment head 20 on the patient. The buoyancy is a force that generally opposes the movement of the treatment head towards the patient and must be accounted for when calculating the force applied to the patient by the robotic arm. As will be appreciated, application of force on the patient can move or shift the soft tissues of the patient, and potentially result in movement of the treatment volume, lesion or tumor being treated leading to image fusion issues as described below. Though the ultrasound probe 22 may not necessarily contact the membrane 48 and impart force on the patient, in some instances such contact and application of force is necessary to ensure that the application of therapy from the therapy transducer 18 reaches the −Z distal-most (from the treatment head 20) portions of the lesion or tumor. As noted above, a resistance indicator 222 as depicted in
Following the instructions on the UI 500, at step 602 the imaging probe 22 is extended from the treatment head 20 such that it extends beyond the therapy transducer 18 and the user can drive the robotic arm 14 and treatment head 20 to locate a target area or region of interest using for example the space mouse 36. During the process, live ultrasound images 502 are acquired and displayed in a panel 504 of the UI 500. Reference images selected during the session (see
At step 610 the imaging probe is moved to the −Y position, as depicted in imaging probe position indicators 505. Once the imaging probe 22 is so positioned, a breath hold may be initiated on the patient to minimize movement of the patient caused by respiration at step 612 and an ultrasound sweep is initiated at step 614 by selection of button 507. The breath hold may be continued for the duration of the ultrasound sweep, and in some embodiments, the ultrasound sweep time is less than the breath hold. During the ultrasound sweep, as shown in
At step 620 a review images panel 514 is depicted on the UI 500 (
If the fusion step is not skipped, and once the recording is saved at step 626, the next button 523 is selected and the workflow progress to the UI 500 depicted in
As will be appreciated, to improve the rigid and/or deformable registration of the ultrasound and pre-procedural images, it may be desirable to place markers as close to the tumor or lesion as possible. This could include the center of the lesion or target, if visible in the ultrasound, or at a boundary of the lesion or tumor, however, other locations away from the lesion may also be employed. In one embodiment these locations are within about 5 cm of the lesion or tumor. This proximity assists in compensating for any deformation of the soft tissues of the patient caused by the placement of the coupling assembly (and medium) on the patient's chest. The volume of the coupling medium is generally between about 10 and 20 liters of fluid, and the weight of any portion of this fluid may compress the soft tissues causing them to shift from the positions they were in during the capture of the pre-procedure images. By finding landmarks in proximity to the lesion or tumor, ultimately the target for therapy, the registration in this area is enhanced, and the effects of compression the coupling medium reduced. In some examples, peri-procedural imaging (MRI, CT, CBCT, etc.) may be acquired with patient coupling in place to allow for accounting of any body deformation due to coupling itself. In other examples, the patient baseline pre-procedural imaging may be acquired in the appropriate set up position for treatment. For example, if treatment is to be conducted in the lateral decubitis position, pre/peri-procedural images may be acquired in this position.
If at step 634 sufficient landmarks or structures have been identified, the fuse button 532 can be selected, and the application stored on the memory in the computing device on the cart 12 fuses the pre- or peri-procedure images with the ultrasound images to displays the axial view in panel 504 and the sagittal view in panel 506 in
To perform a fusion of images a variety of different methods may be employed as is known in the art. An exemplary fusion process can include a process which involves steps such as first, grossly orienting the ultrasound and pre-procedural or peri-procedural image volumes based on the system-to-patient orientations, such as that set at 412, above. Next, the fusion process may seek to align the marked registration points in both the ultrasound images and the pre-procedural or peri-procedural images to be spatially within 10 cm of each other. Next, a deformation model can be applied to the pre-procedural or peri-procedural image volume to account for compression due to the coupling medium being placed on the patient. The ultrasound volume does not require the deformation model because the images acquired via the ultrasound sweep already reflect the deformation from the coupling medium. Finally, an image-based algorithm is engaged which seeks to match structures between the two image volumes. The result is a registration and ultimately a fusion of the ultrasound images from the ultrasound sweep and the pre-procedural or peri-procedural images as depicted in
The sliders 524 allow a user to scroll through the fused images in both panels 504 and 506 and view the fused images (step 638) to determine whether the fusion is sufficiently close to enable planning of a therapy volume and treatment plan (described below).
If adjustments may be required (yes at step 640) there are two options, first a back button 534 may be selected, returning the method to step 628 to move or place new markers 528 as described above upon selecting the fuse button 532 (
If registration point adjustments are not sufficient to result in an acceptable fusion, advanced adjustments (yes at step 641) are available through the Advanced Settings button 536 (
Once all desired manual alignments are completed and the desired divergence set the fuse button 532 may be selected and the application again fuses the pre-procedural or peri-procedure images with the ultrasound images, taking into account the adjustment made, and then returns to step 638 for review of the fusion where the axial view in panel 504 and the sagittal view in panel 506 are displayed as shown in per
If the fusion is acceptable (no at steps 640 and 641), the live fusion can be undertaken by selecting the next button 537 (
The images appear in
Once live fusion is available as in
A number of reasons may result in the fusion being unacceptable. First the ultrasound sweep images were acquired during a breath hold with the lungs generally inflated, which can cause some movement of the anatomy within the patient. In contrast the live ultrasound images are acquired during normal tidal breathing. Secondly, the registration points may not have been correctly identified in the separate imaging data, or they may have been selected too far from the tumor or lesion. Further, the divergence limit may have been selected to large, resulting in potential mismatches of images. Any or all of these along with other bases may be the cause of an unacceptable fusion requiring a renewed adjustment or even a re-sweep of the ultrasound probe 22.
In other embodiments, the DICOM data comprising the pre-procedure imaging may also be modified in various manners, including various segmentations (organs, structures, unwanted tissue volumes, etc.), pre-plans comprising simulated contours and placement of, and/or other visualization features that may be used to inform targeting and localization and treatment planning in subsequent work-flow steps. In some examples, treatment plans may be displayed over the pre-plans, including the display of the contours (described in greater detail below) with may be distinct in their features from the pre-plan (e.g., represented as a different line type, thickness and color than the “contours”).
Following completion of the set-up method 400 the workflow described in this disclosure and optionally the fusion process of method 600, the workflow proceeds to a planning stage. At this stage, the clinician can plan one or more histotripsy therapies for a given patient. The workflow also allows for the clinician to recall and display prior treatment therapies and/or treatment plans so that additional overlapping or non-overlapping therapies can be planned. The UI 700 switches the indicators 702 from highlighting the “Localize” tab to highlighting the “Plan” tab, after planning is completed the “Treat” tab will be highlighted. These tabs allow for a user to understand where in the workflow the user is at any point during the procedure. The planning stage is described in connection with method 800 described by the flow chart in
UI 700 includes a number of buttons 704 that allow for different aspects of the planning process that follows to be undertaken. These buttons 704 include a “Contour Diameter” button, “Margin Size” button, and a “Focus” button. In certain embodiments, these buttons 704 may display as “Contour Diameter”, “Margin Diameter” and “Focal Steering”. It should be understood that contour Diameter means the contour diameter of the lesion or tumor of interest, which in some embodiments may be up to and including 3 cm. The Margin Size or Margin Diameter provides an additional 0.5 cm around each side of the contour, which for the diameter contour may be about 1 cm in total. In certain embodiments, various combinations of the contour diameter and margin size/diameter may be 4 cm in total. Selection of one of these buttons allows various parameters of the procedure to be planned or adjusted as described hereinbelow. It should be further noted that the various displays on the UI, including but not limited to contours, margins, focal points, and/or indicator/field lines may be selectively displayed or removed from UI display during specific timepoints in the user workflow, which may enable better visualization of the lesion of interest during planning or treatment.
In
Upon exiting the localized portions of the workflow (e.g., method 400 followed optionally by method 600 thus either with or without fusion) UI 700 is displayed and an initial target contour 728, is automatically displayed. The target contour 728 is the initial representation of the shape of a tumor or lesion to be treated In one embodiment, the default target contour 728 has initial dimensions of 20 mm along each of the X, Y. and Z axes, as noted by indicators 730. As described below, the value denoted in the indicators 730 can be adjusted by knobs 28, and thus the target contour 728 can be adjusted to more closely match the target contour 728 to the actual shape and size of the tumor or lesion to be treated. In addition using the space mouse 36 and X, Y and Z knobs 28 functionality the location of the target contour 728 can be moved to a more appropriate location if determined by user. A margin indicator 732 is also depicted around the target contour 728 and depicts a volume of tissue around the target contour 728 that will also receive therapy to ensure that the lesion or tumor is entirely treated. As will be described in detail below, the size of the margin indicator 732 defines a boundary around the target contour 728 that is a set value (e.g., 2, 4, 6 mm) that may also be adjusted by the user or system to increase or decrease the margin around the tumor or lesion being treated.
The method 800 starts with step 802, where the treatment head 20 is positioned using either the freedrive buttons 44 or a space mouse 36 operably connected to the robotic arm 14 such that the imaging probe 22 is located at the general area of the mark optionally placed on the patient in connection at step 408 of method 400. As noted above, the ultrasound probe 22 is capturing ultrasound images for display in field 710, and the treatment head 20 is moved such that the tumor or lesion to be treated can be observed in the live ultrasound images 706. Additionally or alternatively, the tumor or lesion to be treated may be identified using surround/adjacent anatomical landmarks. For example, this may be particularly useful when direct visualization is at least partially obscured or limited. This may require movement of the treatment head 20 around the mark to ensure that an acoustic pathway volume 722 and field lines 724 are substantially free from obstructions or blockage (e.g., ribs, cartilage, bowel, GI gas, etc.) that can impact the energy requirements to effectuate therapy of the lesion or tumor.
The UI 700 is configured to allow a user to create and display a planned treatment volume. As noted above, planned treatment volume includes a target contour 728, around the tumor or lesion and a margin contour 732, around the target contour 728. Both margin contour 732 and target contour 728 are configurable by the user. Further a default configuration, as shown in
A planned treatment volume may be displayed to users through the UI 700 in various ways, including but not limited to 2D views of fields 710 and 712 or the 3D model of field 716, and using real-time or live streaming imaging data, or previously collected pre-procedure images (CT, MRI, etc.), or peri-procedural imaging acquired during the procedure (cone beam CT, intraoperative CT, etc.) that are fused to the real-time imaging data. The planned treatment volume may be displayed as graphical features or computer-generated overlays or models, which may further display key plan features or therapy transducer related features analogous to the acoustic field lines including a geometric focus or focal points 726, default therapy focus based on predicted aberration/attenuation, and such features may change position or location dynamically based on motion of the robot or position of the imaging probe 22. Further details of generation of the treatment volume and displaying the treatment volume on the UI 700 are outlined in conjunction with method 800 below.
Upon entry into the UI 700, (e.g., following accepting the fusion at step 652) the application automatically selects the contour diameter button 704 for illumination and it is in with respect to the target contour 728 that initial planning is undertaken. The user may optionally select the margin size or the focus steering buttons, described in greater detail below. Accordingly at step 804 the user ensures the contour diameter button is highlighted. At step 806 the treatment head 20, with the imaging probe 22 viewing in the YZ plane (e.g., the axial plane of the patient), is moved by driving the robotic arm 14 using the space mouse 36 or freedrive feature until the target contour 728 is centered on the target tumor or lesion in the YZ plane. Note while moving the treatment head, resistance to movement experienced by the robotic arm 14 is observed and displayed at all times and movement is slowed if resistance exceeds predefined thresholds, as described further below. Once the target contour 728 is approximately centered over the tumor or lesion the Y and Z the dimensions of the default target contour 728 are adjusted using knobs 28, to change the dimensions of the target contour 728 in each of Y and Z dimensions, the adjustment of which is depicted graphically in indicators 730.
Along with ensuring that the target contour 728 is centered on the tumor or lesion, while moving the robotic arm 14 and imaging probe 22, the acoustic field lines 724 are displayed on the UI 700. During this movement, the user can use the field lines 724 as a guide to facilitate minimal intersections with blocking structures (e.g., bone or other tissues) that can negatively impact the performance of the therapy by increasing the energy needed to achieve therapy. Alternately, the field lines 724 can be used to confirm the histotripsy treatment window with knowledge of any intervening structures. In order to reduce intersection with blocking structures, the treatment arm menu 733 may be opened and motion type of the robotic arm 14 may be limited to rotation only. Then space mouse 36 is used to rotate the position of the treatment head 20, while the target contour position 728 is maintained over the tumor or lesion. Target contour position 728 may also be maintained over/adjacent anatomical landmarks as directed by the user when direct visualization may be obscured. Confirmation that the acoustic pathway is free from obstruction at step 808 can be performed simultaneously with step 806. Alternately, confirmation that the acoustic pathway is preferable including obstructions can be performed here as well. In particular, the 3-D volumetric view illustrated in at least field 716 may provide acoustic pathway information to the user.
At step 810, the imaging probe 22 is rotated 90 degrees as shown with reference to position indictor 219 in
Following steps 810 and 812, the imaging probe is rotated back 90 degrees to view the YZ imaging plane (e.g. axial plane of the patient) at step 813 to confirm the target contour 728 remain centered on the target tumor or lesion and the acoustic field contains the minimal amount of blocking structures. If necessary, the process is repeated from step 806 through step 812 until the contours are centered on the tumor or lesion and the acoustic field is optimized in both or more than one imaging planes.
Next, using one of the knobs 28, as depicted in indicator 730 the margin size can be adjusted at step 814. As shown in
At step 816, following selection of the focus button 704 in
Once the user is satisfied that the target contour 728 and margin contour 732 substantially conform to the tumor or lesion over the entirety of the tumor or lesion and that the field lines 724 define a volume that is substantially free from obstructions over the entirety of the tumor or lesion (or the preferred acoustic window has been achieved including obstructions), the user may select the a next button 738 to initiate a plan verification step at step 818 and the UI 700 as shown in
In some examples, the user may be allowed to “lock” the contours and treatment plan in 3D space as displayed on the UI, and further allowed to robotically survey around the plan to inspect adjacent anatomical spaces/locations and/or organs and structures. This step may be used to help assess plan position for procedures using fusion wherein the ultrasound visualization of the tumor itself is challenging, but the tissue imaging is adequate. In this example, the user may use anatomical landmarks or structures in the DICOM data (e.g., MRI or CT or CBCT) to verify the tumor and plan location. In other examples, the user may simply use this feature to assess plan parameters and placement in the streaming ultrasound. In some examples, wherein sensitive organs (pancreas) and/or structures (bowel) may be close to the plan, this may enable users to assess the treatment site in greater detail and perspective. In some configurations, with the plan locked, the system may comprise return to plan or survey point features (and graphics and UI inputs) to allow the system to automatically position the plan back to the center point (and/or other plan location) per the users discretion/desire.
Once the system includes a locked plan, that locked plan may be stored or linked with a specific treatment protocol (and tumor) or a specific patient. If additional treatments are required or preferred, the locked plan may be accessible in the future such that once the patient is positioned for treatment, the histotripsy system 10 may be configured to recall the locked treatment plan such that the robot arm may be automatically driven within 3D space and the therapy transducer positioned and aligned with a center point (or an alternative identified point) within the locked plan. By aligning with a locked plan, the patient set-up including localization and specific steps of the planning steps may be omitted. In some cases, the UI may be configured to also show markings of previous user selected plan locations, including where the user has assessed the potential placement of the treatment plan, including the display of potential crosshair locations (e.g., as a plan center point), of a representative potential treatment plan. In one example, the system software may allow the user to assess multiple plan locations, wherein allowing the user to mark those locations, enabling the system software to store the position and pose of the robot, allowing the user to return to previous plan locations as desired. In another example, this functionality may be configured to allow assessing and positioning multiple treatment plans in context to one another in 3D space, including allowing the user to overlap treatment plans and/or space them apart, as defined by the user.
An interactive, representative graphic of the target contours 740 is shown on the UI 700 in
At any point during plan verification, (e.g., following display of mitigation measures) a user may select one of the buttons 704 and adjust the target contour 728, the margin contour 732 or the focus 726 at step 833 (as those features were described above) and then re-enter plan verification, as described above, without navigating away from the UI 700 depicted in
In addition, as shown in
As can be expected, moving the treatment head 20 such that the focal point 726 is at the +Z survey point 739 is likely to meet the most resistance, thus in accordance with one aspect of the disclosure at least the +Z and −Z survey points are driven to using steps 820-836 in another aspect all of the survey points 739 are driven to ensure that during a treatment phase, resistance exceeding the second threshold is never experienced. Further, other protocols for limiting motion when breaching one or more thresholds may be employed as described elsewhere herein.
Following selection of the next button 746, the UI 700 depicts the image of
If at any point the target contour 728 or margin 732 are found not to align with the tumor or lesion through the breathing cycle, as observed on the real-time ultrasound and/or using other imaging data, the adjust plan button 752 may be selected and the method return to step 804 where the target contour 728 is redefined. However, if the plan is verified at steps 840 and 842, the accept plan button 754 may be selected to move to treatment.
At various points during the localization, planning, or treatment phases of a procedure, the robotic arm 14 and the treatment head 20 may encounter resistance to motion and/or increased force feedback. Due to said resistance, forces and potential collisions, the system may be configured to store/record the pose and position of the robotic arm and treatment plan and/or target location, to allow users to locate and/or return to the respective pose, positions and locations should the system encounter resistance and/or force requiring the treatment head to be positioned away from the patient. Further, part this resistance to motion, at least generally in the −Z direction, is the buoyancy of the treatment head 20, which may be accounted for and/or continuously calculated and removed from the resistance measurement, as described in of method 400. During motion and movement of the robotic arm 14 and the treatment head 20, the Histotripsy system 10 monitors the resistance (forces acting on the treatment head opposite the direction of motion) caused by physical interactions of the treatment head and the coupling assembly 46 or the patient. As the treatment head 20 is moved to each survey point, or otherwise moved about the patient, understanding resistance and force interactions ensure the therapy transducer 18 can deliver Histotripsy to all portion of the target contour 728 and the margin 732 without injury or damage the equipment or patient. Further, as noted elsewhere pressure applied to the patient, via the treatment head 20 can also cause the soft tissues of the patient to potentially move, shift or distort/deform. This distortion and/or deformation, may be problematic when utilizing the fusion application (described above) or the 3D fusion models 718 resulting in a potential induced image-to-body divergence. Thus, in creating the 3D fusion model, and subsequent treatment plan, the force or pressure applied to the patient by the by the treatment head 20 must be kept at and/or below a defined threshold to ensure that target contour 728 and margin 732 accurately reflect the tumor or lesion to be treated and that the areas of the patient to receive therapy are not distorted which can result in incomplete therapy, or application of therapy to tissues outside target contour 728 or margin 732. In some system embodiments, the fusion model may include various additional sensor inputs to allow tracking movement, distortion and/or deformation, and further enable a dynamic deformable registration model updated to account for such issues.
In accordance with the disclosure, indicators of the magnitude of pressure or force being applied to (or applied against) the patient or resistance to movement of the treatment head 20, may be displayed on the UI as resistance indicator 222 (See e.g., UI 200 in
In one example, a system is configured such that when detected resistance detected is low, automated movements of the robotic arm 14 and the treatment head 20 are not limited, but user directed movements using the freedrive buttons 44 or space mouse 36 may have their speed reduced in the direction of the resistance. When a medium resistance is detected, the manual movement speed may be further reduced in the direction of the resistance and automated movements are again not slowed. When a resistance limit is reached, manual movement in the direction of the resistance is prevented and automated movements are allowed to continue unless a threshold (e.g., 50-newtons of resistance) is reached at which point a soft emergency stop is initiated and an appropriate corrective action message is displayed on the UI. These limits to movement apply during the entire procedure and take into account pressure applied to the treatment head 20 caused by respiration of the patient and well as the buoyancy of the treatment head 20. In this manner, with the buoyancy accounted for and effectively negated, a true value of the force being applied to the treatment head 20 or the resistance caused by the patient's anatomy can be assessed and acted on accordingly.
Once in treatment phase of the work-flow, systems may be configured with several features and steps to enable a bubble cloud detection, visualization, calibration (locating bubble cloud in 2D or 3D space in the imaging to account for any focal shift), aberration correction and threshold determination and setting. These features and steps may be implemented in various ways in effort to best enable usability and user experience In some examples and configurations, the system may guide the user through various steps to initiate therapy to determine one or more of the listed features (e.g., locate the cloud for calibration, etc.). In other configurations, the system may automate the steps and require the user to verify/acknowledge the steps (values established by the system). In addition, various UI graphics or overlays may be used to display these features, as well as associated user-guided text to support the various steps.
In one system configuration, once the target contour 728 and margin 732 have been established and it has been verified that the coupling medium is sufficient and the treatment head 20 may be driven to each of survey points 739 without exceeding the threshold resistance or force values and following selection of the accept button 754 in UI 700 of
The method 1000 starts with an in vivo calibration process, intended to align the focal point indicator 726 to the location of the therapy focus, where the bubble cloud occurs. Note this in vivo calibration step is required in addition to the calibration described in method 100 because of the inherent variation in intervening tissues between treatment head 20 and the tumor which may slightly deflect the focus in different ways. The calibration in method 1000 ensures that the bubble cloud will initially occur near the focal point 726, however the final offset must be uniquely determined for each patient or tumor location by calibrating cloud location to the center of the planned treatment volume. To start, the system automatically moves the treatment head 20 such that the focal point 726 is at the center of the planned treatment volume at step 1002 as shown in
After in vivo calibration, the voltage settings necessary to generate a bubble cloud at each survey point is evaluated in an order set by the application. As shown in
Once a voltage on the indicator 1109 has been increased by rotating the voltage knob 32 such that an acceptable bubble cloud 1104 has been generated at step 1010, which may be accompanied by recognizing a distinct audible tone, generated by the therapy transducer 18 and there has been visual confirmation at step 1012 that the bubble cloud 1104 is centered on the focal point 726 and that the voltage is acceptable at step 1013, the move to next button 1110 may be selected at step 1016. If the user is unsure of the voltage selected, the enable voltage button 1103 may again be selected at optional step 1014 and the voltage changed. This process is repeated until all of the survey points 739 including a center point are navigated to and a voltage applied to the tissue until an acceptable bubble cloud 1104 is generated and the voltages recorded as shown in
Once all of the survey points 739 and the center of the volume defined by the survey points 739 have been navigated to and a voltage recorded for each location, the accept button 1111 becomes available and when selected the UI 1100 updates to that shown in
Each focal location is a volume of tissue which receives histotripsy pulses from the therapy transducer 18 for a given duration. The energy or histotripsy pulses from the therapy transducer 18 causes the cells to burst due to cavitation of the tissue when the focal point is at the focal location 1122 which is evidenced by the bubble cloud 1108, rendering the cells acellular debris that will be reabsorbed by the body. By monitoring the amount of energy directed at a given focal location 1122, and by cycling the energy application on and off at specific durations (as described herein above), a non-thermal ablation of the volume to be treated 1120 is achieved. As will be appreciated, the focal locations 11122 may have some overlap in volume to ensure that complete treatment of the tissue.
At step 1022 an inquiry is made whether all focal locations have received treatment, if not the method progresses to step 1024, where the robotic arm 14 and therapy transducer 18 advance in a stepwise fashion, and in the example provided here a spiral form starting the +Z survey point 739 advancing to each successive focal location 1122. As noted above a variety of different treatment patterns may be employed without departing from the scope of the disclosure. In this way steps 1020 through 1024 are repeated until all focal locations 1122 have received treatment, resulting in the entire volume to be treated 1120 having received treatment. The movement of the robotic arm 14 and therapy transducer 18 is controlled by an application stored on the computing device such that for each successive focal location 1122 the therapy transducer 18 is positioned at a location on the patient where-by the focal point 726 is centered in the focal location 1122 and the bubble cloud 1104 will be generated for that specific focal location 1122. The duration of the application of energy, and period of no energy application before movement to the next focal location 1122 are also controlled by the application, as described herein above.
When all focal locations 1122 have received treatment a yes at step 1022, the UI 1100 advances to the display seen in
The treatment is now complete, but a record of the steps undertaken, the ultrasound images acquired during the procedure, as well as the fusion achieved are stored in memory for future analysis.
If future treatments are planned, the system may be configured such that treatment parameters may be recalled including, but not limited to robotic arm pose, position and treatment head and therapy transducer focus location, bubble cloud offset, voltage thresholds/requirements, target depth and plan/treatment location and parameters. These parameters may be useful, for example, when additional treatments are performed within the same tumor or lesion and/or a one or more additional treatment plans are intended overlapping and/or in proximity to the first plan/treatment.
As an example, when an adjacent treatment may be performed, the Histotripsy system can be configured to recall recent treatment/plan parameters and be automatically positioned (treatment head and robotic arm pose) at the start, endpoint or in any treatment point (focal location or time-based) therebetween.
In another example, the histotripsy system is configured to allow the users to recall/move-to the robot pose used in the previous treatment(s). This will position the treatment head in the same position as before assuming the patient and therapy cart didn't move after the prior treatment(s). The user would need to recall the specifics of the previous treatment plan(s) (XYZ diameter and margin) though, and then decide how to size and position the subsequent treatment plan(s). As previously disclosed, in some configurations, the system may store this information for recall.
In yet another example, the histotripsy system may be configured to display the previous treatment(s) plan contours and plan overlays. Having the previous treatment plan contours shown on the screen along with recall/move-to functionality (Option 1) will give the user a visual aid to plan for overlapping their next treatment. This option again relies on the user to determine the best next treatment plan considering overlap of the previous treatment plan(s) as well as tumor coverage considerations.
In an alternate example, the histotripsy system may be configured to plan all overlapping treatments prior to first therapy delivery. If the user can identify and mark tumors to be treated in 3D space, then the histotripsy system may create and display a recommended multi-treatment plan for the user to review. In some versions of this example, pre and peri-procedural CBCT may be used to enable this capability.
In another embodiment, shown in
Further as a part of cavitation detection described above, in
Upon completion of treatment, various forms of procedure and treatment reports may be provided. Reports may comprise various forms of data, including patient and treatment contextual information (disease type, size, stage, location, etc.), plan parameters (size, location, target and margin contour dimensions, plan depth, plan position in context to target tissue/tumor, etc.), energy settings (thresholds and/or voltage settings across plan points, average voltage, etc.), treatment details (time, etc.). This may further comprise screenshots from the UI, video recordings of the UI or procedure. The information/data may also include any that may have been included and/or utilized for pre-procedure simulation and/or the patient registration process described earlier. The various reports may be exportable to electronic health records or databases, and/or to local networks, media and/or other devices.
In some examples, referring to
Reference is now made to
Application 1218 may further include a user interface 1216 (e.g., UI 200, 500, 700, 1100). Image data may include the pre-procedure CT and MRI scans or other images, ultrasound image data, and 2D and 3D reconstructions derived from the ultrasound image data, including multi-modal computer vision and fusion models. In some embodiments, including when connected to a cone beam CT, the UI may include graphics and instructions for guiding the user through how to set up, import, register, and navigate to the desired target. Processor 1204 may be coupled with memory 1202, display 1206, input device 1210, output module 1212, network interface 1208 and ultrasound imaging device 1215. Workstation 1201 may be a stationary computing device, such as a personal computer, or a portable computing device such as a tablet computer. Workstation 1201 may embed a plurality of computer devices.
For example,
In
The user can optionally add anatomical landmarks to the images as shown in workflow step 5404.
In
Memory 1202 may include any non-transitory computer-readable storage media for storing data and/or software including instructions that are executable by processor 1204 and which control the operation of workstation 1201 and, in some embodiments, may also control the operation of ultrasound imaging device 1215 and the ultrasound treatment device 1217. In an embodiment, memory 1202 may include one or more storage devices such as solid-state storage devices, e.g., flash memory chips. Alternatively, or in addition to the one or more solid-state storage devices, memory 1202 may include one or more mass storage devices connected to the processor 1204 through a mass storage controller (not shown) and a communications bus (not shown).
Although the description of computer-readable media contained herein refers to solid-state storage, it should be appreciated by those skilled in the art that computer-readable storage media can be any available media that can be accessed by the processor 1204. That is, computer readable storage media may include non-transitory, volatile, and non-volatile, removable, and non-removable media implemented in any method or technology for storage of information such as computer-readable instructions, data structures, program modules or other data. For example, computer-readable storage media may include RAM, ROM, EPROM, EEPROM, flash memory or other solid-state memory technology. CD-ROM, DVD, Blu-Ray or other optical storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other medium which may be used to store the desired information, and which may be accessed by workstation 1201.
Application 1218 may, when executed by processor 1204, cause display 1206 to present user interface 1216. User interface 1216 may be configured to present to the user a variety screens including any of
Network interface 1208 may be configured to connect to a network such as a local area network (LAN) consisting of a wired network and/or a wireless network, a wide area network (WAN), a wireless mobile network, a Bluetooth network, and/or the Internet. Network interface 1208 may be used to connect between workstation 1201 and imaging device 1215 or the treatment device 1217. Network interface 1208 may be also used to receive image data 1214. Input device 1210 may be any device by which a user may interact with workstation 1201, such as, for example, a mouse, keyboard, foot pedal, touch screen, and/or voice interface. Output module 1212 may include any connectivity port or bus, such as, for example, parallel ports, serial ports, universal serial busses (USB), or any other similar connectivity port known to those skilled in the art. From the foregoing and with reference to the various figures, those skilled in the art will appreciate that certain modifications can be made to the disclosure without departing from the scope of the disclosure.
While detailed embodiments are disclosed herein, the disclosed embodiments are merely examples of the disclosure, which may be embodied in various forms and aspects. Therefore, specific structural and functional details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the disclosure in virtually any appropriately detailed structure. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto.
This patent application claims priority to U.S. provisional patent application No. 63/497,277, titled “HISTOTRIPSY SET-UP AND PLANNING SYSTEMS AND METHODS”, and filed on Apr. 20, 2023, which is herein incorporated by reference in its entirety.
| Number | Date | Country | |
|---|---|---|---|
| 63497277 | Apr 2023 | US |
