WO2019130107A1 - Determining the state of an ultrasonic end effector - Google Patents

Determining the state of an ultrasonic end effector Download PDF

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Publication number
WO2019130107A1
WO2019130107A1 PCT/IB2018/057939 IB2018057939W WO2019130107A1 WO 2019130107 A1 WO2019130107 A1 WO 2019130107A1 IB 2018057939 W IB2018057939 W IB 2018057939W WO 2019130107 A1 WO2019130107 A1 WO 2019130107A1
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WO
WIPO (PCT)
Prior art keywords
ultrasonic
complex impedance
surgical
generator
control circuit
Prior art date
Application number
PCT/IB2018/057939
Other languages
English (en)
French (fr)
Inventor
Cameron R. NOTT
Fergus P. Quigley
Matthew S. SCHNEIDER
Gregory D. Bishop
Alexander R. CUTI
Maxwell ROCKMAN
Original Assignee
Ethicon Llc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US16/115,247 external-priority patent/US11317937B2/en
Application filed by Ethicon Llc filed Critical Ethicon Llc
Priority to BR112020013093-1A priority Critical patent/BR112020013093B1/pt
Priority to CN201880084585.6A priority patent/CN111526821B/zh
Priority to MX2020006859A priority patent/MX2020006859A/es
Priority to JP2020535545A priority patent/JP7279051B2/ja
Publication of WO2019130107A1 publication Critical patent/WO2019130107A1/en

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    • A61B17/320092—Surgical cutting instruments using mechanical vibrations, e.g. ultrasonic with additional movable means for clamping or cutting tissue, e.g. with a pivoting jaw
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    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
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    • A61B90/06—Measuring instruments not otherwise provided for
    • A61B2090/064—Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension
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Definitions

  • smart energy devices may be needed in a smart energy architecture environment.
  • an ultrasonic surgical instrument comprising: an end effector comprising an ultrasonic blade, an ultrasonic transducer acoustically coupled to the ultrasonic blade, and a control circuit coupled to the ultrasonic transducer.
  • the ultrasonic transducer is configured to ultrasonically oscillate the ultrasonic blade in response to a drive signal.
  • the control circuit is configured to: measure a complex impedance of the ultrasonic transducer, compare the complex impedance to a plurality of reference complex impedance patterns, each of the plurality of reference complex impedance patterns corresponding to a state of the end effector, and determine the state of the end effector according to which of the plurality of reference complex impedance patterns the complex impedance corresponds.
  • an ultrasonic generator for driving an ultrasonic surgical instrument comprising an end effector, an ultrasonic blade, and an ultrasonic transducer acoustically coupled to the ultrasonic blade.
  • the ultrasonic transducer is configured to ultrasonically oscillate the ultrasonic blade in response to a drive signal.
  • the ultrasonic generator comprises a control circuit coupled to the ultrasonic transducer.
  • the control circuit is configured to: apply the drive signal to the ultrasonic transducer, measure a complex impedance of the ultrasonic transducer, compare the complex impedance to a plurality of reference complex impedance patterns, each of the plurality of reference complex impedance patterns corresponding to a state of the end effector, and determine the state of the end effector according to which of the plurality of reference complex impedance patterns the complex impedance corresponds.
  • a method of controlling an ultrasonic surgical instrument comprising an end effector, an ultrasonic blade, and an ultrasonic transducer acoustically coupled to the ultrasonic blade.
  • the ultrasonic transducer is configured to ultrasonically oscillate the ultrasonic blade in response to a drive signal from a generator.
  • the method comprises: measuring, by a control circuit coupled to the ultrasonic transducer, a complex impedance of the ultrasonic transducer; comparing, by the control circuit, the complex impedance to a plurality of reference complex impedance patterns, each of the plurality of reference complex impedance patterns corresponding to a state of the end effector; and determining, by the control circuit, the state of the end effector according to which of the plurality of reference complex impedance patterns the complex impedance corresponds.
  • FIG. 1 is a block diagram of a computer-implemented interactive surgical system, in accordance with at least one aspect of the present disclosure.
  • FIG. 2 is a surgical system being used to perform a surgical procedure in an operating room, in accordance with at least one aspect of the present disclosure.
  • FIG. 3 is a surgical hub paired with a visualization system, a robotic system, and an intelligent instrument, in accordance with at least one aspect of the present disclosure.
  • FIG. 4 is a partial perspective view of a surgical hub enclosure, and of a combo generator module slidably receivable in a drawer of the surgical hub enclosure, in accordance with at least one aspect of the present disclosure.
  • FIG. 5 is a perspective view of a combo generator module with bipolar, ultrasonic, and monopolar contacts and a smoke evacuation component, in accordance with at least one aspect of the present disclosure.
  • FIG. 6 illustrates individual power bus attachments for a plurality of lateral docking ports of a lateral modular housing configured to receive a plurality of modules, in accordance with at least one aspect of the present disclosure.
  • FIG. 7 illustrates a vertical modular housing configured to receive a plurality of modules, in accordance with at least one aspect of the present disclosure.
  • FIG. 8 illustrates a surgical data network comprising a modular communication hub configured to connect modular devices located in one or more operating theaters of a healthcare facility, or any room in a healthcare facility specially equipped for surgical operations, to the cloud, in accordance with at least one aspect of the present disclosure.
  • FIG. 9 illustrates a computer-implemented interactive surgical system, in accordance with at least one aspect of the present disclosure.
  • FIG. 10 illustrates a surgical hub comprising a plurality of modules coupled to the modular control tower, in accordance with at least one aspect of the present disclosure.
  • FIG. 1 1 illustrates one aspect of a Universal Serial Bus (USB) network hub device, in accordance with at least one aspect of the present disclosure.
  • USB Universal Serial Bus
  • FIG. 12 illustrates a logic diagram of a control system of a surgical instrument or tool, in accordance with at least one aspect of the present disclosure.
  • FIG. 13 illustrates a control circuit configured to control aspects of the surgical instrument or tool, in accordance with at least one aspect of the present disclosure.
  • FIG. 14 illustrates a combinational logic circuit configured to control aspects of the surgical instrument or tool, in accordance with at least one aspect of the present disclosure.
  • FIG. 15 illustrates a sequential logic circuit configured to control aspects of the surgical instrument or tool, in accordance with at least one aspect of the present disclosure.
  • FIG. 16 illustrates a surgical instrument or tool comprising a plurality of motors which can be activated to perform various functions, in accordance with at least one aspect of the present disclosure.
  • FIG. 17 is a schematic diagram of a robotic surgical instrument configured to operate a surgical tool described herein, in accordance with at least one aspect of the present disclosure.
  • FIG. 18 illustrates a block diagram of a surgical instrument programmed to control the distal translation of a displacement member, in accordance with at least one aspect of the present disclosure.
  • FIG. 19 is a schematic diagram of a surgical instrument configured to control various functions, in accordance with at least one aspect of the present disclosure.
  • FIG. 20 is a system configured to execute adaptive ultrasonic blade control algorithms in a surgical data network comprising a modular communication hub, in accordance with at least one aspect of the present disclosure.
  • FIG. 21 illustrates an example of a generator, in accordance with at least one aspect of the present disclosure.
  • FIG. 22 is a surgical system comprising a generator and various surgical instruments usable therewith, in accordance with at least one aspect of the present disclosure.
  • FIG. 23 is an end effector, in accordance with at least one aspect of the present disclosure.
  • FIG. 24 is a diagram of the surgical system of FIG. 22, in accordance with at least one aspect of the present disclosure.
  • FIG. 25 is a model illustrating motional branch current, in accordance with at least one aspect of the present disclosure.
  • FIG. 26 is a structural view of a generator architecture, in accordance with at least one aspect of the present disclosure.
  • FIGS. 27A-27C are functional views of a generator architecture, in accordance with at least one aspect of the present disclosure.
  • FIGS. 28A-28B are structural and functional aspects of a generator, in accordance with at least one aspect of the present disclosure.
  • FIG. 29 is a schematic diagram of one aspect of an ultrasonic drive circuit.
  • FIG. 30 is a schematic diagram of a control circuit, in accordance with at least one aspect of the present disclosure.
  • FIG. 31 shows a simplified block circuit diagram illustrating another electrical circuit contained within a modular ultrasonic surgical instrument, in accordance with at least one aspect of the present disclosure.
  • FIG. 32 illustrates a generator circuit partitioned into multiple stages, in accordance with at least one aspect of the present disclosure.
  • FIG. 33 illustrates a generator circuit partitioned into multiple stages where a first stage circuit is common to the second stage circuit, in accordance with at least one aspect of the present disclosure.
  • FIG. 34 is a schematic diagram of one aspect of a drive circuit configured for driving a high-frequency current (RF), in accordance with at least one aspect of the present disclosure.
  • FIG. 35 illustrates one aspect of a fundamental architecture for a digital synthesis circuit such as a direct digital synthesis (DDS) circuit configured to generate a plurality of wave shapes for the electrical signal waveform for use in a surgical instrument, in accordance with at least one aspect of the present disclosure.
  • DDS direct digital synthesis
  • FIG. 36 illustrates one aspect of direct digital synthesis (DDS) circuit configured to generate a plurality of wave shapes for the electrical signal waveform for use in surgical instrument, in accordance with at least one aspect of the present disclosure.
  • DDS direct digital synthesis
  • FIG. 37 illustrates one cycle of a discrete time digital electrical signal waveform, in accordance with at least one aspect of the present disclosure of an analog waveform (shown superimposed over a discrete time digital electrical signal waveform for comparison purposes), in accordance with at least one aspect of the present disclosure.
  • FIG. 38 is a diagram of a control system configured to provide progressive closure of a closure member as it advances distally to close the clamp arm to apply a closure force load at a desired rate according to one aspect of this disclosure.
  • FIG. 39 illustrates a proportional-integral-derivative (PID) controller feedback control system according to one aspect of this disclosure.
  • PID proportional-integral-derivative
  • FIG. 40 is a system diagram of a segmented circuit comprising a plurality of independently operated circuit segments, in accordance with at least one aspect of the present disclosure.
  • FIG. 41 is a circuit diagram of various components of a surgical instrument with motor control functions, in accordance with at least one aspect of the present disclosure.
  • FIG. 42 is an alternative system for controlling the frequency of an ultrasonic electromechanical system and detecting the impedance thereof, in accordance with at least one aspect of the present disclosure.
  • FIG. 43A is a graphical representation of impedance phase angle as a function of resonant frequency of the same ultrasonic device with a cold (blue) and hot (red) ultrasonic blade;
  • FIG. 43B is a graphical representation of impedance magnitude as a function of resonant frequency of the same ultrasonic device with a cold (blue) and hot (red) ultrasonic blade.
  • FIG. 44 is a diagram of a Kalman filter to improve temperature estimator and state space model based on impedance across an ultrasonic transducer measured at a variety of frequencies, in accordance with at least one aspect of the present disclosure.
  • FIG. 45 are three probability distributions employed by a state estimator of the Kalman filter shown in FIG. 44 to maximize estimates, in accordance with at least one aspect of the present disclosure.
  • FIG. 46A is a graphical representation of temperature versus time of an ultrasonic device with no temperature control reaching a maximum temperature of 490°C.
  • FIG. 46B is a graphical representation of temperature versus time of an ultrasonic device with temperature control reaching a maximum temperature of 320°C, in accordance with at least one aspect of the present disclosure.
  • FIGS. 47A-47B are graphical representations of feedback control to adjust ultrasonic power applied to an ultrasonic transducer when a sudden drop in temperature of an ultrasonic blade is detected, where
  • FIG. 47A is a graphical representation of ultrasonic power as a function of time; and [0060] FIG. 47B is a plot of ultrasonic blade temperature as a function of time, in accordance with at least one aspect of the present disclosure.
  • FIG. 48 is a logic flow diagram of a process depicting a control program or a logic configuration to control the temperature of an ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • FIG. 49 is a graphical representation of ultrasonic blade temperature as a function of time during a vessel firing, in accordance with at least one aspect of the present disclosure.
  • FIG. 50 is a logic flow diagram of a process depicting a control program or a logic configuration to control the temperature of an ultrasonic blade between two temperature set points, in accordance with at least one aspect of the present disclosure.
  • FIG. 51 is a logic flow diagram of a process depicting a control program or a logic configuration to determine the initial temperature of an ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • FIG. 52 is a logic flow diagram of a process depicting a control program or a logic configuration to determine when an ultrasonic blade is approaching instability and then adjusting the power to the ultrasonic transducer to prevent instability of the ultrasonic transducer, in accordance with at least one aspect of the present disclosure.
  • FIG. 53 is a logic flow diagram of a process depicting a control program or a logic configuration to provide ultrasonic sealing with temperature control, in accordance with at least one aspect of the present disclosure.
  • FIG. 54 are graphical representations of ultrasonic transducer current and ultrasonic blade temperature as a function of time, in accordance with at least one aspect of the present disclosure.
  • FIG. 55 is a bottom view of an ultrasonic end effector showing a clamp arm and ultrasonic blade delineating tissue positioning within the ultrasonic end effector, in accordance with at least one aspect of the present disclosure.
  • FIG. 56 is a graphical representation depicting change in ultrasonic transducer impedance as a function tissue location within the ultrasonic end effector over a range of predetermined ultrasonic generator power level increases, in accordance with at least one aspect of the present disclosure.
  • FIG. 57 is a graphical representation depicting change in ultrasonic transducer impedance as a function of time relative to the location of tissue within the ultrasonic end effector, in accordance with at least one aspect of the present disclosure.
  • FIG. 58 is a logic flow diagram of a process depicting a control program or a logic configuration to identify operation in a non-therapeutic range of power applied to the ultrasonic transducer to determine tissue positioning, in accordance with at least one aspect of the present disclosure.
  • FIG. 59 illustrates one aspect of an end effector of an ultrasonic surgical instrument comprising infrared (IR) sensors located on the jaw member, in accordance with at least one aspect of the present disclosure.
  • IR infrared
  • FIG. 60 illustrates one aspect of a flexible circuit on which the IR sensors shown in FIG. 59 may be mounted or formed integrally with, in accordance to one aspect of the present disclosure.
  • FIG. 61 is a sectional view of an ultrasonic end effector comprising a clamp arm and an ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • FIG. 62 illustrates IR refractivity detection sensor circuits mounted on a flexible circuit substrate shown in plan view, in accordance with at least one aspect of the present disclosure.
  • FIG. 63 is a logic flow diagram of a process depicting a control program or a logic configuration to measure IR reflectance to determine tissue composition to tune the amplitude of the ultrasonic transducer, in accordance with at least one aspect of the present disclosure.
  • FIG. 64A is a graphical representation of the rate of closure of the clamp arm versus time to identify the collagen transformation point according to various aspects of the present disclosure where time is shown along the horizontal axis and change in clamp arm position is shown along the vertical axis, in accordance with at least one aspect of the present disclosure.
  • FIG. 64B is a magnified portion of the graphical representation shown in FIG. 64A.
  • FIG. 65 is a logic flow diagram of a process depicting a control program or a logic configuration to detect the collagen transformation point to control the rate of closure of the of the clamp arm or the amplitude of the ultrasonic transducer, in accordance with at least one aspect of the present disclosure.
  • FIG. 66 is a graphical representation of the identification of the collagen transformation temperature point to identify the collagen/elastin ratio according to various aspects of the present disclosure, where tissue temperature is shown along the horizontal axis and ultrasonic transducer impedance is shown along the vertical axis, in accordance with at least one aspect of the present disclosure.
  • FIG. 67 is a logic flow diagram of a process depicting a control program or a logic configuration to identify the collagen transformation temperature to identify the collagen/elastin ratio, in accordance with at least one aspect of the present disclosure.
  • FIG. 68 is a graphical representation of the distribution of compression load across an ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • FIG. 69 is a graphical representation of pressure applied to tissue versus time, in accordance with at least one aspect of the present disclosure.
  • FIG. 70 illustrates an end effector including a single-jaw electrode array for detecting tissue location, in accordance with at least one aspect of the present disclosure.
  • FIG. 71 is an activation matrix for the single-jaw electrode array of FIG. 70, in accordance with at least one aspect of the present disclosure.
  • FIG. 72 illustrates an end effector including a dual-jaw electrode array for detecting tissue location, in accordance with at least one aspect of the present disclosure.
  • FIG. 73 is an activation matrix for the dual-jaw electrode array of FIG. 72, in
  • FIG. 74 illustrates opposing sets of electrodes overlaid a tissue grasped by an end effector corresponding to the activation matrix on FIG. 73, in accordance with at least one aspect of the present disclosure.
  • FIG. 75 illustrates an end effector including dual-jaw segmented electrode array, according to at least one aspect of the present disclosure.
  • FIG. 76 illustrates a tissue overlaid a jaw including a segmented electrode array, according to at least one aspect of the present disclosure.
  • FIG. 77 is a schematic diagram of a segmented electrode array circuit including band pass filters, in accordance with at least one aspect of the present disclosure.
  • FIG. 78 is a graphical representation of the frequency response corresponding to the tissue grasped in FIG. 76, in accordance with at least one aspect of the present disclosure.
  • FIG. 79 is a graphical representation of the frequency of the ultrasonic transducer system as a function of drive frequency and ultrasonic blade temperature drift, in accordance with at least one aspect of the present disclosure.
  • FIG. 80 is a graphical representation of temperature of the ultrasonic transducer as a function of time, in accordance with at least one aspect of the present disclosure.
  • FIG. 81 is a graphical representation of the modal shift of resonant frequency based on the temperature of the ultrasonic blade moving the resonant frequency as a function of the temperature of the ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • FIG. 82 is a spectra of an ultrasonic surgical instrument with a variety of different states and conditions of the end effector where phase and magnitude of the impedance of an ultrasonic transducer are plotted as a function of frequency, in accordance with at least one aspect of the present disclosure.
  • FIG. 83 is a methodology for classification of data based on a set of training data S, where ultrasonic transducer impedance magnitude and phase are plotted as a function of frequency, in accordance with at least one aspect of the present disclosure.
  • FIG. 84 is a logic flow diagram depicting a control program or a logic configuration to determine jaw conditions based on the complex impedance characteristic pattern (fingerprint), in accordance with at least one aspect of the present disclosure.
  • FIG. 85 is a timeline depicting situational awareness of a surgical hub, in accordance with at least one aspect of the present disclosure. DESCRIPTION
  • a computer-implemented interactive surgical system 100 includes one or more surgical systems 102 and a cloud-based system (e.g., the cloud 104 that may include a remote server 1 13 coupled to a storage device 105).
  • a cloud-based system e.g., the cloud 104 that may include a remote server 1 13 coupled to a storage device 105.
  • Each surgical system 102 includes at least one surgical hub 106 in communication with the cloud 104 that may include a remote server 1 13.
  • the surgical system 102 includes a visualization system 108, a robotic system 1 10, and a handheld intelligent surgical instrument 1 12, which are configured to communicate with one another and/or the hub 106.
  • a surgical system 102 may include an M number of hubs 106, an N number of visualization systems 108, an O number of robotic systems 1 10, and a P number of handheld intelligent surgical instruments 1 12, where M, N, O, and P are integers greater than or equal to one.
  • FIG. 3 depicts an example of a surgical system 102 being used to perform a surgical procedure on a patient who is lying down on an operating table 1 14 in a surgical operating room 1 16.
  • a robotic system 1 10 is used in the surgical procedure as a part of the surgical system 102.
  • the robotic system 1 10 includes a surgeon’s console 1 18, a patient side cart 120 (surgical robot), and a surgical robotic hub 122.
  • the patient side cart 120 can manipulate at least one removably coupled surgical tool 1 17 through a minimally invasive incision in the body of the patient while the surgeon views the surgical site through the surgeon’s console 1 18.
  • An image of the surgical site can be obtained by a medical imaging device 124, which can be manipulated by the patient side cart 120 to orient the imaging device 124.
  • the robotic hub 122 can be used to process the images of the surgical site for subsequent display to the surgeon through the surgeon’s console 1 18.
  • the imaging device 124 includes at least one image sensor and one or more optical components.
  • Suitable image sensors include, but are not limited to, Charge- Coupled Device (CCD) sensors and Complementary Metal-Oxide Semiconductor (CMOS) sensors.
  • CCD Charge- Coupled Device
  • CMOS Complementary Metal-Oxide Semiconductor
  • the optical components of the imaging device 124 may include one or more illumination sources and/or one or more lenses.
  • the one or more illumination sources may be directed to illuminate portions of the surgical field.
  • the one or more image sensors may receive light reflected or refracted from the surgical field, including light reflected or refracted from tissue and/or surgical instruments.
  • the one or more illumination sources may be configured to radiate electromagnetic energy in the visible spectrum as well as the invisible spectrum.
  • the visible spectrum sometimes referred to as the optical spectrum or luminous spectrum, is that portion of the electromagnetic spectrum that is visible to (i.e., can be detected by) the human eye and may be referred to as visible light or simply light.
  • a typical human eye will respond to wavelengths in air that are from about 380 nm to about 750 nm.
  • the invisible spectrum i.e., the non-luminous spectrum
  • the invisible spectrum is that portion of the electromagnetic spectrum that lies below and above the visible spectrum (i.e., wavelengths below about 380 nm and above about 750 nm).
  • the invisible spectrum is not detectable by the human eye. Wavelengths greater than about 750 nm are longer than the red visible spectrum, and they become invisible infrared (IR), microwave, and radio electromagnetic radiation.
  • Wavelengths less than about 380 nm are shorter than the violet spectrum, and they become invisible ultraviolet, x-ray, and gamma ray electromagnetic radiation.
  • the imaging device 124 is configured for use in a minimally invasive procedure.
  • imaging devices suitable for use with the present disclosure include, but not limited to, an arthroscope, angioscope, bronchoscope, choledochoscope, colonoscope, cytoscope, duodenoscope, enteroscope, esophagogastro-duodenoscope (gastroscope), endoscope, laryngoscope, nasopharyngo-neproscope, sigmoidoscope, thoracoscope, and ureteroscope.
  • the imaging device employs multi-spectrum monitoring to discriminate topography and underlying structures.
  • a multi-spectral image is one that captures image data within specific wavelength ranges across the electromagnetic spectrum. The wavelengths may be separated by filters or by the use of instruments that are sensitive to particular wavelengths, including light from frequencies beyond the visible light range, e.g., IR and ultraviolet. Spectral imaging can allow extraction of additional information the human eye fails to capture with its receptors for red, green, and blue.
  • the use of multi-spectral imaging is described in greater detail under the heading“Advanced Imaging Acquisition Module” in U.S. Provisional Patent Application Serial No. 62/61 1 ,341 , titled INTERACTIVE SURGICAL PLATFORM, filed
  • Multi-spectrum monitoring can be a useful tool in relocating a surgical field after a surgical task is completed to perform one or more of the previously described tests on the treated tissue.
  • the sterile field may be considered a specified area, such as within a tray or on a sterile towel, that is considered free of microorganisms, or the sterile field may be considered an area, immediately around a patient, who has been prepared for a surgical procedure.
  • the sterile field may include the scrubbed team members, who are properly attired, and all furniture and fixtures in the area.
  • the visualization system 108 includes one or more imaging sensors, one or more image-processing units, one or more storage arrays, and one or more displays that are strategically arranged with respect to the sterile field, as illustrated in FIG. 2.
  • the visualization system 108 includes an interface for HL7, PACS, and EMR.
  • a primary display 1 19 is positioned in the sterile field to be visible to an operator at the operating table 1 14.
  • a visualization tower 1 1 1 is positioned outside the sterile field.
  • the visualization tower 1 1 1 includes a first non-sterile display 107 and a second non-sterile display 109, which face away from each other.
  • the visualization system 108 guided by the hub 106, is configured to utilize the displays 107, 109, and 1 19 to coordinate information flow to operators inside and outside the sterile field.
  • the hub 106 may cause the visualization system 108 to display a snapshot of a surgical site, as recorded by an imaging device 124, on a non-sterile display 107 or 109, while maintaining a live feed of the surgical site on the primary display 1 19.
  • the snapshot on the non-sterile display 107 or 109 can permit a non-sterile operator to perform a diagnostic step relevant to the surgical procedure, for example.
  • the hub 106 is also configured to route a diagnostic input or feedback entered by a non-sterile operator at the visualization tower 1 1 1 to the primary display 1 19 within the sterile field, where it can be viewed by a sterile operator at the operating table.
  • the input can be in the form of a modification to the snapshot displayed on the non- sterile display 107 or 109, which can be routed to the primary display 1 19 by the hub 106.
  • a surgical instrument 1 12 is being used in the surgical procedure as part of the surgical system 102.
  • the hub 106 is also configured to coordinate information flow to a display of the surgical instrument 1 12.
  • a diagnostic input or feedback entered by a non-sterile operator at the visualization tower 1 1 1 can be routed by the hub 106 to the surgical instrument display 1 15 within the sterile field, where it can be viewed by the operator of the surgical instrument 1 12.
  • Example surgical instruments that are suitable for use with the surgical system 102 are described under the heading SURGICAL INSTRUMENT HARDWARE and in U.S. Provisional Patent Application Serial No. 62/61 1 ,341 , titled
  • a hub 106 is depicted in communication with a visualization system 108, a robotic system 1 10, and a handheld intelligent surgical instrument 1 12.
  • the hub 106 includes a hub display 135, an imaging module 138, a generator module 140, a
  • the hub 106 further includes a smoke evacuation module 126 and/or a suction/irrigation module 128.
  • the surgical hub for use in a surgical procedure that involves energy application to tissue at a surgical site.
  • the surgical hub includes a hub enclosure and a combo generator module slidably receivable in a docking station of the hub enclosure.
  • the docking station includes data and power contacts.
  • the combo generator module includes two or more of an ultrasonic energy generator component, a bipolar RF energy generator component, and a monopolar RF energy generator component that are housed in a single unit.
  • the combo generator module also includes a smoke evacuation component, at least one energy delivery cable for connecting the combo generator module to a surgical instrument, at least one smoke evacuation component configured to evacuate smoke, fluid, and/or particulates generated by the application of therapeutic energy to the tissue, and a fluid line extending from the remote surgical site to the smoke evacuation component.
  • the fluid line is a first fluid line and a second fluid line extends from the remote surgical site to a suction and irrigation module slidably received in the hub enclosure.
  • the hub enclosure comprises a fluid interface.
  • Certain surgical procedures may require the application of more than one energy type to the tissue.
  • One energy type may be more beneficial for cutting the tissue, while another different energy type may be more beneficial for sealing the tissue.
  • a bipolar generator can be used to seal the tissue while an ultrasonic generator can be used to cut the sealed tissue.
  • a hub modular enclosure 136 is configured to accommodate different generators, and facilitate an interactive communication therebetween.
  • One of the advantages of the hub modular enclosure 136 is enabling the quick removal and/or replacement of various modules.
  • the modular surgical enclosure includes a first energy-generator module, configured to generate a first energy for application to the tissue, and a first docking station comprising a first docking port that includes first data and power contacts, wherein the first energy-generator module is slidably movable into an electrical engagement with the power and data contacts and wherein the first energy-generator module is slidably movable out of the electrical engagement with the first power and data contacts,
  • the modular surgical enclosure also includes a second energy- generator module configured to generate a second energy, different than the first energy, for application to the tissue, and a second docking station comprising a second docking port that includes second data and power contacts, wherein the second energy-generator module is slidably movable into an electrical engagement with the power and data contacts, and wherein the second energy-generator module is slidably movable out of the electrical engagement with the second power and data contacts.
  • the modular surgical enclosure also includes a communication bus between the first docking port and the second docking port, configured to facilitate
  • the generator module 140 can be a generator module with integrated monopolar, bipolar, and ultrasonic components supported in a single housing unit 139 slidably insertable into the hub modular enclosure 136.
  • the generator module 140 can be configured to connect to a monopolar device 146, a bipolar device 147, and an ultrasonic device 148.
  • the generator module 140 may comprise a series of monopolar, bipolar, and/or ultrasonic generator modules that interact through the hub modular enclosure 136.
  • the hub modular enclosure 136 can be configured to facilitate the insertion of multiple generators and interactive communication between the generators docked into the hub modular enclosure 136 so that the generators would act as a single generator.
  • the hub modular enclosure 136 comprises a modular power and communication backplane 149 with external and wireless communication headers to enable the removable attachment of the modules 140, 126, 128 and interactive communication
  • the hub modular enclosure 136 includes docking stations, or drawers, 151 , herein also referred to as drawers, which are configured to slidably receive the modules 140, 126, 128.
  • FIG. 4 illustrates a partial perspective view of a surgical hub enclosure 136, and a combo generator module 145 slidably receivable in a docking station 151 of the surgical hub enclosure 136.
  • a docking port 152 with power and data contacts on a rear side of the combo generator module 145 is configured to engage a corresponding docking port 150 with power and data contacts of a corresponding docking station 151 of the hub modular enclosure 136 as the combo generator module 145 is slid into position within the corresponding docking station 151 of the hub module enclosure 136.
  • the combo generator module 145 includes a bipolar, ultrasonic, and monopolar module and a smoke evacuation module integrated together into a single housing unit 139, as illustrated in FIG. 5.
  • the smoke evacuation module 126 includes a fluid line 154 that conveys captured/collected smoke and/or fluid away from a surgical site and to, for example, the smoke evacuation module 126.
  • Vacuum suction originating from the smoke evacuation module 126 can draw the smoke into an opening of a utility conduit at the surgical site.
  • the utility conduit, coupled to the fluid line, can be in the form of a flexible tube terminating at the smoke evacuation module 126.
  • the utility conduit and the fluid line define a fluid path extending toward the smoke evacuation module 126 that is received in the hub enclosure 136.
  • the suction/irrigation module 128 is coupled to a surgical tool comprising an aspiration fluid line and a suction fluid line.
  • the aspiration and suction fluid lines are in the form of flexible tubes extending from the surgical site toward the suction/irrigation module 128.
  • One or more drive systems can be configured to cause irrigation and aspiration of fluids to and from the surgical site.
  • the surgical tool includes a shaft having an end effector at a distal end thereof and at least one energy treatment associated with the end effector, an aspiration tube, and an irrigation tube.
  • the aspiration tube can have an inlet port at a distal end thereof and the aspiration tube extends through the shaft.
  • an irrigation tube can extend through the shaft and can have an inlet port in proximity to the energy deliver implement.
  • the energy deliver implement is configured to deliver ultrasonic and/or RF energy to the surgical site and is coupled to the generator module 140 by a cable extending initially through the shaft.
  • the irrigation tube can be in fluid communication with a fluid source, and the aspiration tube can be in fluid communication with a vacuum source.
  • the fluid source and/or the vacuum source can be housed in the suction/irrigation module 128.
  • the fluid source and/or the vacuum source can be housed in the hub enclosure 136 separately from the suction/irrigation module 128.
  • a fluid interface can be configured to connect the suction/irrigation module 128 to the fluid source and/or the vacuum source.
  • the modules 140, 126, 128 and/or their corresponding docking stations on the hub modular enclosure 136 may include alignment features that are configured to align the docking ports of the modules into engagement with their counterparts in the docking stations of the hub modular enclosure 136.
  • the combo generator module 145 includes side brackets 155 that are configured to slidably engage with
  • brackets 156 of the corresponding docking station 151 of the hub modular enclosure 136 cooperate to guide the docking port contacts of the combo generator module 145 into an electrical engagement with the docking port contacts of the hub modular enclosure 136.
  • the drawers 151 of the hub modular enclosure 136 are the same, or substantially the same size, and the modules are adjusted in size to be received in the drawers 151 .
  • the side brackets 155 and/or 156 can be larger or smaller depending on the size of the module.
  • the drawers 151 are different in size and are each designed to accommodate a particular module.
  • the contacts of a particular module can be keyed for engagement with the contacts of a particular drawer to avoid inserting a module into a drawer with mismatching contacts.
  • the docking port 150 of one drawer 151 can be coupled to the docking port 150 of another drawer 151 through a communications link 157 to facilitate an interactive communication between the modules housed in the hub modular enclosure 136.
  • the docking ports 150 of the hub modular enclosure 136 may alternatively, or additionally, facilitate a wireless interactive communication between the modules housed in the hub modular enclosure 136. Any suitable wireless communication can be employed, such as for example Air Titan-Bluetooth.
  • FIG. 6 illustrates individual power bus attachments for a plurality of lateral docking ports of a lateral modular housing 160 configured to receive a plurality of modules of a surgical hub 206.
  • the lateral modular housing 160 is configured to laterally receive and interconnect the modules 161 .
  • the modules 161 are slidably inserted into docking stations 162 of lateral modular housing 160, which includes a backplane for interconnecting the modules 161 .
  • the modules 161 are arranged laterally in the lateral modular housing 160.
  • the modules 161 may be arranged vertically in a lateral modular housing.
  • FIG. 7 illustrates a vertical modular housing 164 configured to receive a plurality of modules 165 of the surgical hub 106.
  • the modules 165 are slidably inserted into docking stations, or drawers, 167 of vertical modular housing 164, which includes a backplane for interconnecting the modules 165.
  • the drawers 167 of the vertical modular housing 164 are arranged vertically, in certain instances, a vertical modular housing 164 may include drawers that are arranged laterally.
  • the modules 165 may interact with one another through the docking ports of the vertical modular housing 164.
  • a display 177 is provided for displaying data relevant to the operation of the modules 165.
  • the vertical modular housing 164 includes a master module 178 housing a plurality of sub-modules that are slidably received in the master module 178.
  • the imaging module 138 comprises an integrated video processor and a modular light source and is adapted for use with various imaging devices.
  • the imaging device is comprised of a modular housing that can be assembled with a light source module and a camera module.
  • the housing can be a disposable housing.
  • the disposable housing is removably coupled to a reusable controller, a light source module, and a camera module.
  • the light source module and/or the camera module can be selectively chosen depending on the type of surgical procedure.
  • the camera module comprises a CCD sensor.
  • the camera module comprises a CMOS sensor.
  • the camera module is configured for scanned beam imaging.
  • the light source module can be configured to deliver a white light or a different light, depending on the surgical procedure.
  • the module imaging device of the present disclosure is configured to permit the replacement of a light source module or a camera module midstream during a surgical procedure, without having to remove the imaging device from the surgical field.
  • the imaging device comprises a tubular housing that includes a plurality of channels.
  • a first channel is configured to slidably receive the camera module, which can be configured for a snap-fit engagement with the first channel.
  • a second channel is configured to slidably receive the light source module, which can be configured for a snap-fit engagement with the second channel.
  • the camera module and/or the light source module can be rotated into a final position within their respective channels.
  • a threaded engagement can be employed in lieu of the snap-fit engagement.
  • multiple imaging devices are placed at different positions in the surgical field to provide multiple views.
  • the imaging module 138 can be configured to switch between the imaging devices to provide an optimal view.
  • the imaging module 138 can be configured to integrate the images from the different imaging device.
  • FIG. 8 illustrates a surgical data network 201 comprising a modular communication hub 203 configured to connect modular devices located in one or more operating theaters of a healthcare facility, or any room in a healthcare facility specially equipped for surgical operations, to a cloud-based system (e.g., the cloud 204 that may include a remote server 213 coupled to a storage device 205).
  • the modular communication hub 203 comprises a network hub 207 and/or a network switch 209 in communication with a network router.
  • the modular communication hub 203 also can be coupled to a local computer system 210 to provide local computer processing and data manipulation.
  • the surgical data network 201 may be configured as passive, intelligent, or switching.
  • a passive surgical data network serves as a conduit for the data, enabling it to go from one device (or segment) to another and to the cloud computing resources.
  • An intelligent surgical data network includes additional features to enable the traffic passing through the surgical data network to be monitored and to configure each port in the network hub 207 or network switch 209.
  • An intelligent surgical data network may be referred to as a manageable hub or switch.
  • a switching hub reads the destination address of each packet and then forwards the packet to the correct port.
  • Modular devices 1 a-1 n located in the operating theater may be coupled to the modular communication hub 203.
  • the network hub 207 and/or the network switch 209 may be coupled to a network router 21 1 to connect the devices 1 a-1 n to the cloud 204 or the local computer system 210.
  • Data associated with the devices 1 a-1 n may be transferred to cloud-based computers via the router for remote data processing and manipulation.
  • Data associated with the devices 1 a-1 n may also be transferred to the local computer system 210 for local data processing and manipulation.
  • Modular devices 2a-2m located in the same operating theater also may be coupled to a network switch 209.
  • the network switch 209 may be coupled to the network hub 207 and/or the network router 21 1 to connect to the devices 2a-2m to the cloud 204.
  • Data associated with the devices 2a-2n may be transferred to the cloud 204 via the network router 21 1 for data processing and manipulation.
  • Data associated with the devices 2a- 2m may also be transferred to the local computer system 210 for local data processing and manipulation.
  • the surgical data network 201 may be expanded by interconnecting multiple network hubs 207 and/or multiple network switches 209 with multiple network routers 21 1.
  • the modular communication hub 203 may be contained in a modular control tower configured to receive multiple devices 1 a-1 n/2a-2m.
  • the local computer system 210 also may be contained in a modular control tower.
  • the modular communication hub 203 is connected to a display 212 to display images obtained by some of the devices 1 a-1 n/2a-2m, for example during surgical procedures.
  • the devices 1 a-1 n/2a-2m may include, for example, various modules such as an imaging module 138 coupled to an endoscope, a generator module 140 coupled to an energy-based surgical device, a smoke evacuation module 126, a suction/irrigation module 128, a communication module 130, a processor module 132, a storage array 134, a surgical device coupled to a display, and/or a non-contact sensor module, among other modular devices that may be connected to the modular communication hub 203 of the surgical data network 201 .
  • various modules such as an imaging module 138 coupled to an endoscope, a generator module 140 coupled to an energy-based surgical device, a smoke evacuation module 126, a suction/irrigation module 128, a communication module 130, a processor module 132, a storage array 134, a surgical device coupled to a display, and/or a non-contact sensor module, among other modular devices that may be connected to the modular communication hub 203 of the surgical data network 201 .
  • the surgical data network 201 may comprise a combination of network hub(s), network switch(es), and network router(s) connecting the devices 1 a-1 n/2a-2m to the cloud. Any one of or all of the devices 1 a-1 n/2a-2m coupled to the network hub or network switch may collect data in real time and transfer the data to cloud computers for data processing and manipulation. It will be appreciated that cloud computing relies on sharing computing resources rather than having local servers or personal devices to handle software applications.
  • the word“cloud” may be used as a metaphor for“the Internet,” although the term is not limited as such. Accordingly, the term“cloud computing” may be used herein to refer to“a type of Internet-based computing,” where different services— such as servers, storage, and
  • the cloud infrastructure may be maintained by a cloud service provider.
  • the cloud service provider may be the entity that coordinates the usage and control of the devices 1 a-1 n/2a-2m located in one or more operating theaters.
  • the cloud computing services can perform a large number of calculations based on the data gathered by smart surgical instruments, robots, and other computerized devices located in the operating theater.
  • the hub hardware enables multiple devices or connections to be connected to a computer that communicates with the cloud computing resources and storage.
  • the surgical data network provides improved surgical outcomes, reduced costs, and improved patient satisfaction.
  • At least some of the devices 1 a-1 n/2a-2m may be employed to view tissue states to assess leaks or perfusion of sealed tissue after a tissue sealing and cutting procedure.
  • At least some of the devices 1 a-1 n/2a-2m may be employed to identify pathology, such as the effects of diseases, using the cloud-based computing to examine data including images of samples of body tissue for diagnostic purposes. This includes localization and margin confirmation of tissue and phenotypes.
  • At least some of the devices 1 a- 1 n/2a-2m may be employed to identify anatomical structures of the body using a variety of sensors integrated with imaging devices and techniques such as overlaying images captured by multiple imaging devices.
  • the data gathered by the devices 1 a-1 n/2a-2m, including image data, may be transferred to the cloud 204 or the local computer system 210 or both for data processing and manipulation including image processing and manipulation.
  • the data may be analyzed to improve surgical procedure outcomes by determining if further treatment, such as the application of endoscopic intervention, emerging technologies, a targeted radiation, targeted intervention, and precise robotics to tissue-specific sites and conditions, may be pursued.
  • Such data analysis may further employ outcome analytics processing, and using standardized approaches may provide beneficial feedback to either confirm surgical treatments and the behavior of the surgeon or suggest modifications to surgical treatments and the behavior of the surgeon.
  • the operating theater devices 1 a-1 n may be connected to the modular communication hub 203 over a wired channel or a wireless channel depending on the configuration of the devices 1 a-1 n to a network hub.
  • the network hub 207 may be implemented, in one aspect, as a local network broadcast device that works on the physical layer of the Open System Interconnection (OSI) model.
  • the network hub provides connectivity to the devices l a i n located in the same operating theater network.
  • the network hub 207 collects data in the form of packets and sends them to the router in half duplex mode.
  • the network hub 207 does not store any media access control/Internet Protocol (MAC/IP) to transfer the device data.
  • MAC/IP media access control/Internet Protocol
  • the network hub 207 has no routing tables or intelligence regarding where to send information and broadcasts all network data across each connection and to a remote server 213 (FIG. 9) over the cloud 204.
  • the network hub 207 can detect basic network errors such as collisions, but having all information broadcast to multiple ports can be a security risk and cause bottlenecks.
  • the operating theater devices 2a-2m may be connected to a network switch 209 over a wired channel or a wireless channel.
  • the network switch 209 works in the data link layer of the OSI model.
  • the network switch 209 is a multicast device for connecting the devices 2a-2m located in the same operating theater to the network.
  • the network switch 209 sends data in the form of frames to the network router 21 1 and works in full duplex mode.
  • Multiple devices 2a-2m can send data at the same time through the network switch 209.
  • the network switch 209 stores and uses MAC addresses of the devices 2a-2m to transfer data.
  • the network hub 207 and/or the network switch 209 are coupled to the network router 21 1 for connection to the cloud 204.
  • the network router 21 1 works in the network layer of the OSI model.
  • the network router 21 1 creates a route for transmitting data packets received from the network hub 207 and/or network switch 21 1 to cloud-based computer resources for further processing and manipulation of the data collected by any one of or all the devices 1 a-1 n/2a-2m.
  • the network router 21 1 may be employed to connect two or more different networks located in different locations, such as, for example, different operating theaters of the same healthcare facility or different networks located in different operating theaters of different healthcare facilities.
  • the network router 21 1 sends data in the form of packets to the cloud 204 and works in full duplex mode. Multiple devices can send data at the same time.
  • the network router 21 1 uses IP addresses to transfer data.
  • the network hub 207 may be implemented as a USB hub, which allows multiple USB devices to be connected to a host computer.
  • the USB hub may expand a single USB port into several tiers so that there are more ports available to connect devices to the host system computer.
  • the network hub 207 may include wired or wireless capabilities to receive information over a wired channel or a wireless channel.
  • a wireless USB short-range, high-bandwidth wireless radio communication protocol may be employed for communication between the devices 1 a-1 n and devices 2a-2m located in the operating theater.
  • the operating theater devices 1 a-1 n/2a-2m may communicate to the modular communication hub 203 via Bluetooth wireless technology standard for exchanging data over short distances (using short-wavelength UHF radio waves in the ISM band from 2.4 to 2.485 GHz) from fixed and mobile devices and building personal area networks (PANs).
  • PANs personal area networks
  • the operating theater devices 1 a-1 n/2a-2m may communicate to the modular communication hub 203 via a number of wireless or wired communication standards or protocols, including but not limited to Wi-Fi (IEEE 802.1 1 family), WiMAX (IEEE 802.16 family), IEEE 802.20, long-term evolution (LTE), and Ev-DO, HSPA+, HSDPA+, HSUPA+, EDGE, GSM, GPRS, CDMA, TDMA, DECT, and Ethernet derivatives thereof, as well as any other wireless and wired protocols that are designated as 3G, 4G, 5G, and beyond.
  • the computing module may include a plurality of communication modules.
  • a first communication module may be dedicated to shorter-range wireless communications such as Wi-Fi and Bluetooth
  • a second communication module may be dedicated to longer-range wireless communications such as GPS, EDGE, GPRS, CDMA, WiMAX, LTE, Ev-DO, and others.
  • the modular communication hub 203 may serve as a central connection for one or all of the operating theater devices 1 a-1 n/2a-2m and handles a data type known as frames.
  • Frames carry the data generated by the devices 1 a-1 n/2a-2m.
  • a frame is received by the modular communication hub 203, it is amplified and transmitted to the network router 21 1 , which transfers the data to the cloud computing resources by using a number of wireless or wired communication standards or protocols, as described herein.
  • the modular communication hub 203 can be used as a standalone device or be connected to compatible network hubs and network switches to form a larger network.
  • the modular communication hub 203 is generally easy to install, configure, and maintain, making it a good option for networking the operating theater devices 1 a-1 n/2a-2m.
  • FIG. 9 illustrates a computer-implemented interactive surgical system 200.
  • the computer-implemented interactive surgical system 200 is similar in many respects to the computer-implemented interactive surgical system 100.
  • the computer- implemented interactive surgical system 200 includes one or more surgical systems 202, which are similar in many respects to the surgical systems 102.
  • Each surgical system 202 includes at least one surgical hub 206 in communication with a cloud 204 that may include a remote server 213.
  • the computer-implemented interactive surgical system 200 comprises a modular control tower 236 connected to multiple operating theater devices such as, for example, intelligent surgical instruments, robots, and other computerized devices located in the operating theater. As shown in FIG.
  • the modular control tower 236 comprises a modular communication hub 203 coupled to a computer system 210.
  • the modular control tower 236 is coupled to an imaging module 238 that is coupled to an endoscope 239, a generator module 240 that is coupled to an energy device 241 , a smoke evacuator module 226, a suction/irrigation module 228, a communication module 230, a processor module 232, a storage array 234, a smart device/instrument 235 optionally coupled to a display 237, and a non-contact sensor module 242.
  • the operating theater devices are coupled to cloud computing resources and data storage via the modular control tower 236.
  • a robot hub 222 also may be connected to the modular control tower 236 and to the cloud computing resources.
  • the devices/instruments 235, visualization systems 208, among others, may be coupled to the modular control tower 236 via wired or wireless communication standards or protocols, as described herein.
  • the modular control tower 236 may be coupled to a hub display 215 (e.g., monitor, screen) to display and overlay images received from the imaging module, device/instrument display, and/or other visualization systems 208.
  • the hub display also may display data received from devices connected to the modular control tower in conjunction with images and overlaid images.
  • FIG. 10 illustrates a surgical hub 206 comprising a plurality of modules coupled to the modular control tower 236.
  • the modular control tower 236 comprises a modular communication hub 203, e.g., a network connectivity device, and a computer system 210 to provide local processing, visualization, and imaging, for example.
  • the modular communication hub 203 may be connected in a tiered configuration to expand the number of modules (e.g., devices) that may be connected to the modular communication hub 203 and transfer data associated with the modules to the computer system 210, cloud computing resources, or both.
  • each of the network hubs/switches in the modular communication hub 203 includes three downstream ports and one upstream port.
  • the upstream network hub/switch is connected to a processor to provide a communication connection to the cloud computing resources and a local display 217. Communication to the cloud 204 may be made either through a wired or a wireless communication channel.
  • the surgical hub 206 employs a non-contact sensor module 242 to measure the dimensions of the operating theater and generate a map of the surgical theater using either ultrasonic or laser-type non-contact measurement devices.
  • An ultrasound-based non-contact sensor module scans the operating theater by transmitting a burst of ultrasound and receiving the echo when it bounces off the perimeter walls of an operating theater as described under the heading“Surgical Hub Spatial Awareness Within an Operating Room” in U.S. Provisional Patent Application Serial No. 62/61 1 ,341 , titled INTERACTIVE SURGICAL PLATFORM, filed
  • a laser-based non-contact sensor module scans the operating theater by transmitting laser light pulses, receiving laser light pulses that bounce off the perimeter walls of the operating theater, and comparing the phase of the transmitted pulse to the received pulse to determine the size of the operating theater and to adjust Bluetooth pairing distance limits, for example.
  • the computer system 210 comprises a processor 244 and a network interface 245.
  • the processor 244 is coupled to a communication module 247, storage 248, memory 249, non volatile memory 250, and input/output interface 251 via a system bus.
  • the system bus can be any of several types of bus structure(s) including the memory bus or memory controller, a peripheral bus or external bus, and/or a local bus using any variety of available bus
  • ISA Industrial Standard Architecture
  • MSA Micro-Charmel Architecture
  • EISA Extended ISA
  • IDE Intelligent Drive Electronics
  • VLB VESA Local Bus
  • PCI Peripheral Component Interconnect
  • USB Universal Serial Bus
  • AGP Advanced Graphics Port
  • PCMCIA Personal Computer Memory Card International Association bus
  • SCSI Small Computer Systems Interface
  • the processor 244 may be any single-core or multicore processor such as those known under the trade name ARM Cortex by Texas Instruments.
  • the processor may be an LM4F230H5QR ARM Cortex-M4F Processor Core, available from Texas
  • Instruments for example, comprising an on-chip memory of 256 KB single-cycle flash memory, or other non-volatile memory, up to 40 MHz, a prefetch buffer to improve performance above 40 MHz, a 32 KB single-cycle serial random access memory (SRAM), an internal read-only memory (ROM) loaded with Stel laris Ware® software, a 2 KB electrically erasable
  • EEPROM programmable read-only memory
  • PWM pulse width modulation
  • QEI quadrature encoder inputs
  • ADCs 12-bit analog-to-digital converters
  • the processor 244 may comprise a safety controller comprising two controller-based families such as TMS570 and RM4x, known under the trade name Hercules ARM Cortex R4, also by Texas Instruments.
  • the safety controller may be configured specifically for IEC 61508 and ISO 26262 safety critical applications, among others, to provide advanced integrated safety features while delivering scalable performance, connectivity, and memory options.
  • the system memory includes volatile memory and non-volatile memory.
  • the basic input/output system (BIOS) containing the basic routines to transfer information between elements within the computer system, such as during start-up, is stored in non-volatile memory.
  • the non-volatile memory can include ROM, programmable ROM (PROM), electrically programmable ROM (EPROM), EEPROM, or flash memory.
  • Volatile memory includes random-access memory (RAM), which acts as external cache memory.
  • RAM random-access memory
  • RAM is available in many forms such as SRAM, dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (DDR SDRAM), enhanced SDRAM (ESDRAM), Synchlink DRAM (SLDRAM), and direct Rambus RAM (DRRAM).
  • DRAM dynamic RAM
  • SDRAM synchronous DRAM
  • DDR SDRAM double data rate SDRAM
  • ESDRAM enhanced SDRAM
  • SLDRAM Synchlink DRAM
  • DRRAM direct Rambus RAM
  • the computer system 210 also includes removable/non-removable, volatile/non volatile computer storage media, such as for example disk storage.
  • the disk storage includes, but is not limited to, devices like a magnetic disk drive, floppy disk drive, tape drive, Jaz drive, Zip drive, LS-60 drive, flash memory card, or memory stick.
  • the disk storage can include storage media separately or in combination with other storage media including, but not limited to, an optical disc drive such as a compact disc ROM device (CD-ROM), compact disc recordable drive (CD-R Drive), compact disc rewritable drive (CD-RW Drive), or a digital versatile disc ROM drive (DVD-ROM).
  • CD-ROM compact disc ROM
  • CD-R Drive compact disc recordable drive
  • CD-RW Drive compact disc rewritable drive
  • DVD-ROM digital versatile disc ROM drive
  • a removable or non-removable interface may be employed.
  • the computer system 210 includes software that acts as an intermediary between users and the basic computer resources described in a suitable operating environment.
  • Such software includes an operating system.
  • the operating system which can be stored on the disk storage, acts to control and allocate resources of the computer system.
  • System applications take advantage of the management of resources by the operating system through program modules and program data stored either in the system memory or on the disk storage. It is to be appreciated that various components described herein can be implemented with various operating systems or combinations of operating systems.
  • a user enters commands or information into the computer system 210 through input device(s) coupled to the I/O interface 251.
  • the input devices include, but are not limited to, a pointing device such as a mouse, trackball, stylus, touch pad, keyboard, microphone, joystick, game pad, satellite dish, scanner, TV tuner card, digital camera, digital video camera, web camera, and the like.
  • These and other input devices connect to the processor through the system bus via interface port(s).
  • the interface port(s) include, for example, a serial port, a parallel port, a game port, and a USB.
  • the output device(s) use some of the same types of ports as input device(s).
  • a USB port may be used to provide input to the computer system and to output information from the computer system to an output device.
  • An output adapter is provided to illustrate that there are some output devices like monitors, displays, speakers, and printers, among other output devices that require special adapters.
  • the output adapters include, by way of illustration and not limitation, video and sound cards that provide a means of connection between the output device and the system bus. It should be noted that other devices and/or systems of devices, such as remote computer(s), provide both input and output capabilities.
  • the computer system 210 can operate in a networked environment using logical connections to one or more remote computers, such as cloud computer(s), or local computers.
  • the remote cloud computer(s) can be a personal computer, server, router, network PC, workstation, microprocessor-based appliance, peer device, or other common network node, and the like, and typically includes many or all of the elements described relative to the computer system. For purposes of brevity, only a memory storage device is illustrated with the remote computer(s).
  • the remote co puter(s) is logically connected to the computer system through a network interface and then physically connected via a communication connection.
  • the network interface encompasses communication networks such as local area networks (LANs) and wide area networks (WANs).
  • LAN technologies include Fiber Distributed Data Interface (FDDI), Copper Distributed Data Interface (CDDI), Ethernet/IEEE 802.3, Token Ring/IEEE 802.5 and the like.
  • WAN technologies include, but are not limited to, point-to-point links, circuit- switching networks like Integrated Services Digital Networks (ISDN) and variations thereon, packet switching networks, and Digital Subscriber Lines (DSL).
  • ISDN Integrated Services Digital Networks
  • DSL Digital Subscriber Lines
  • the computer system 210 of FIG. 10, the imaging module 238 and/or visualization system 208, and/or the processor module 232 of FIGS. 9-10 may comprise an image processor, image-processing engine, media processor, or any specialized digital signal processor (DSP) used for the processing of digital images.
  • the image processor may employ parallel computing with single instruction, multiple data (SIMD) or multiple instruction, multiple data (MIMD) technologies to increase speed and efficiency.
  • SIMD single instruction, multiple data
  • MIMD multiple instruction, multiple data
  • the digital image- processing engine can perform a range of tasks.
  • the image processor may be a system on a chip with multicore processor architecture.
  • the communication connection(s) refers to the hardware/software employed to connect the network interface to the bus. While the communication connection is shown for illustrative clarity inside the computer system, it can also be external to the computer system 210.
  • the hardware/software necessary for connection to the network interface includes, for illustrative purposes only, internal and external technologies such as modems, including regular telephone-grade modems, cable modems, and DSL modems, ISDN adapters, and Ethernet cards.
  • FIG. 1 1 illustrates a functional block diagram of one aspect of a USB network hub 300 device, in accordance with at least one aspect of the present disclosure.
  • the USB network hub device 300 employs a TUSB2036 integrated circuit hub by Texas Instruments.
  • the USB network hub 300 is a CMOS device that provides an upstream USB transceiver port 302 and up to three downstream USB transceiver ports 304, 306, 308 in compliance with the USB 2.0 specification.
  • the upstream USB transceiver port 302 is a differential root data port comprising a differential data minus (DM0) input paired with a differential data plus (DP0) input.
  • DM0 differential data minus
  • DP0 differential data plus
  • the three downstream USB transceiver ports 304, 306, 308 are differential data ports where each port includes differential data plus (DP1 -DP3) outputs paired with differential data minus (DM1 -DM3) outputs.
  • the USB network hub 300 device is implemented with a digital state machine instead of a microcontroller, and no firmware programming is required. Fully compliant USB
  • the USB network hub 300 device may be configured either in bus-powered or self-powered mode and includes a hub power logic 312 to manage power.
  • the USB network hub 300 device includes a serial interface engine 310 (SIE).
  • SIE 310 is the front end of the USB network hub 300 hardware and handles most of the protocol described in chapter 8 of the USB specification.
  • the SIE 310 typically comprehends signaling up to the transaction level.
  • the functions that it handles could include: packet recognition, transaction sequencing, SOP, EOP, RESET, and RESUME signal detection/generation, clock/data separation, non-return-to-zero invert (NRZI) data encoding/decoding and bit-stuffing, CRC generation and checking (token and data), packet ID (PID) generation and
  • the 310 receives a clock input 314 and is coupled to a suspend/resume logic and frame timer 316 circuit and a hub repeater circuit 318 to control communication between the upstream USB transceiver port 302 and the downstream USB transceiver ports 304, 306, 308 through port logic circuits 320, 322, 324.
  • the SIE 310 is coupled to a command decoder 326 via interface logic to control commands from a serial EEPROM via a serial EEPROM interface 330.
  • the USB network hub 300 can connect 127 functions configured in up to six logical layers (tiers) to a single computer. Further, the USB network hub 300 can connect to all peripherals using a standardized four-wire cable that provides both
  • the power configurations are bus-powered and self- powered modes.
  • the USB network hub 300 may be configured to support four modes of power management: a bus-powered hub, with either individual-port power management or ganged-port power management, and the self-powered hub, with either individual-port power management or ganged-port power management.
  • the USB network hub 300, the upstream USB transceiver port 302 is plugged into a USB host controller, and the downstream USB transceiver ports 304, 306, 308 are exposed for connecting USB compatible devices, and so forth.
  • FIG. 12 illustrates a logic diagram of a control system 470 of a surgical instrument or tool in accordance with one or more aspects of the present disclosure.
  • the system 470 comprises a control circuit.
  • the control circuit includes a microcontroller 461 comprising a processor 462 and a memory 468.
  • One or more of sensors 472, 474, 476 for example, provide real-time feedback to the processor 462.
  • a tracking system 480 is configured to determine the position of the longitudinally movable displacement member.
  • the position information is provided to the processor 462, which can be programmed or configured to determine the position of the longitudinally movable drive member as well as the position of the closure member. Additional motors may be provided at the tool driver interface to control closure tube travel, shaft rotation, articulation, or clamp arm closure, or a combination of the above.
  • a display 473 displays a variety of operating conditions of the instruments and may include touch screen functionality for data input. Information displayed on the display 473 may be overlaid with images acquired via endoscopic imaging modules.
  • the microcontroller 461 may be any single-core or multicore processor such as those known under the trade name ARM Cortex by Texas Instruments.
  • the main microcontroller 461 may be an LM4F230H5QR ARM Cortex-M4F Processor Core, available from Texas Instruments, for example, comprising an on-chip memory of 256 KB single-cycle flash memory, or other non-volatile memory, up to 40 MHz, a prefetch buffer to improve performance above 40 MHz, a 32 KB single-cycle SRAM, and internal ROM loaded with StellarisWare® software, a 2 KB EEPROM, one or more PWM modules, one or more QEI analogs, and/or one or more 12-bit ADCs with 12 analog input channels, details of which are available for the product datasheet.
  • the microcontroller 461 may comprise a safety controller comprising two controller-based families such as TMS570 and RM4x, known under the trade name Hercules ARM Cortex R4, also by Texas Instruments.
  • the safety controller may be configured specifically for IEC 61508 and ISO 26262 safety critical applications, among others, to provide advanced integrated safety features while delivering scalable performance, connectivity, and memory options.
  • the microcontroller 461 may be programmed to perform various functions such as precise control over the speed and position of the knife, articulation systems, clamp arm, or a combination of the above.
  • the microcontroller 461 includes a processor 462 and a memory 468.
  • the electric motor 482 may be a brushed direct current (DC) motor with a gearbox and mechanical links to an articulation or knife system.
  • a motor driver 492 may be an A3941 available from Allegro Microsystems, Inc. Other motor drivers may be readily substituted for use in the tracking system 480 comprising an absolute positioning system. A detailed description of an absolute positioning system is described in U.S. Patent Application Publication No. 2017/0296213, titled SYSTEMS AND METHODS FOR
  • the microcontroller 461 may be programmed to provide precise control over the speed and position of displacement members and articulation systems.
  • the microcontroller 461 may be configured to compute a response in the software of the microcontroller 461.
  • the computed response is compared to a measured response of the actual system to obtain an“observed” response, which is used for actual feedback decisions.
  • the observed response is a favorable, tuned value that balances the smooth, continuous nature of the simulated response with the measured response, which can detect outside influences on the system.
  • the motor 482 may be controlled by the motor driver 492 and can be employed by the firing system of the surgical instrument or tool.
  • the motor 482 may be a brushed DC driving motor having a maximum rotational speed of approximately 25,000 RPM.
  • the motor 482 may include a brushless motor, a cordless motor, a synchronous motor, a stepper motor, or any other suitable electric motor.
  • the motor driver 492 may comprise an H-bridge driver comprising field-effect transistors (FETs), for example.
  • FETs field-effect transistors
  • the motor 482 can be powered by a power assembly releasably mounted to the handle assembly or tool housing for supplying control power to the surgical instrument or tool.
  • the power assembly may comprise a battery which may include a number of battery cells connected in series that can be used as the power source to power the surgical instrument or tool.
  • the battery cells of the power assembly may be replaceable and/or rechargeable battery cells.
  • the battery cells can be lithium-ion batteries which can be couplable to and separable from the power assembly.
  • the motor driver 492 may be an A3941 available from Allegro Microsystems, Inc.
  • the A3941 492 is a full-bridge controller for use with external N-channel power metal-oxide semiconductor field-effect transistors (MOSFETs) specifically designed for inductive loads, such as brush DC motors.
  • the driver 492 comprises a unique charge pump regulator that provides full (>10 V) gate drive for battery voltages down to 7 V and allows the A3941 to operate with a reduced gate drive, down to 5.5 V.
  • a bootstrap capacitor may be employed to provide the above battery supply voltage required for N-channel MOSFET s.
  • An internal charge pump for the high- side drive allows DC (100% duty cycle) operation.
  • the full bridge can be driven in fast or slow decay modes using diode or synchronous rectification.
  • current recirculation can be through the high-side or the low-side FETs.
  • the power FETs are protected from shoot-through by resistor-adjustable dead time.
  • Integrated diagnostics provide indications of undervoltage, overtemperature, and power bridge faults and can be configured to protect the power MOSFETs under most short circuit conditions.
  • Other motor drivers may be readily substituted for use in the tracking system 480 comprising an absolute positioning system.
  • the tracking system 480 comprises a controlled motor drive circuit arrangement comprising a position sensor 472 according to one aspect of this disclosure.
  • the position sensor 472 for an absolute positioning system provides a unique position signal corresponding to the location of a displacement member.
  • the displacement member represents a longitudinally movable drive member comprising a rack of drive teeth for meshing engagement with a corresponding drive gear of a gear reducer assembly.
  • the displacement member represents the firing member, which could be adapted and configured to include a rack of drive teeth.
  • the displacement member represents a longitudinal displacement member to open and close a clamp arm, which can be adapted and configured to include a rack of drive teeth.
  • the displacement member represents a clamp arm closure member configured to close and to open a clamp arm of a stapler, ultrasonic, or electrosurgical device, or combinations of the above.
  • the term displacement member is used generically to refer to any movable member of the surgical instrument or tool such as the drive member, the clamp arm, or any element that can be displaced. Accordingly, the absolute positioning system can, in effect, track the displacement of the clamp arm by tracking the linear displacement of the longitudinally movable drive member.
  • the absolute positioning system can be configured to track the position of a clamp arm in the process of closing or opening.
  • the displacement member may be coupled to any position sensor 472 suitable for measuring linear displacement.
  • the longitudinally movable drive member, or clamp arm, or combinations thereof may be coupled to any suitable linear displacement sensor.
  • Linear displacement sensors may include contact or non-contact displacement sensors.
  • Linear displacement sensors may comprise linear variable differential transformers (LVDT), differential variable reluctance transducers (DVRT), a slide potentiometer, a magnetic sensing system comprising a movable magnet and a series of linearly arranged Hall effect sensors, a magnetic sensing system comprising a fixed magnet and a series of movable, linearly arranged Hall effect sensors, an optical sensing system comprising a movable light source and a series of linearly arranged photo diodes or photo detectors, an optical sensing system comprising a fixed light source and a series of movable linearly, arranged photo diodes or photo detectors, or any combination thereof.
  • LVDT linear variable differential transformers
  • DVRT differential variable reluctance transducers
  • slide potentiometer a magnetic sensing system comprising a movable magnet and a series of linearly arranged Hall effect sensors
  • a magnetic sensing system comprising a fixed magnet and a series of movable, linearly arranged Hall effect sensors
  • the electric motor 482 can include a rotatable shaft that operably interfaces with a gear assembly that is mounted in meshing engagement with a set, or rack, of drive teeth on the displacement member.
  • a sensor element may be operably coupled to a gear assembly such that a single revolution of the position sensor 472 element corresponds to some linear longitudinal translation of the displacement member.
  • An arrangement of gearing and sensors can be connected to the linear actuator, via a rack and pinion arrangement, or a rotary actuator, via a spur gear or other connection.
  • a power source supplies power to the absolute positioning system and an output indicator may display the output of the absolute positioning system.
  • the displacement member represents the longitudinally movable drive member comprising a rack of drive teeth formed thereon for meshing engagement with a corresponding drive gear of the gear reducer assembly.
  • the displacement member represents the longitudinally movable firing member to open and close a clamp arm.
  • a single revolution of the sensor element associated with the position sensor 472 is equivalent to a longitudinal linear displacement di of the of the displacement member, where di is the longitudinal linear distance that the displacement member moves from point“a” to point “b” after a single revolution of the sensor element coupled to the displacement member.
  • the sensor arrangement may be connected via a gear reduction that results in the position sensor 472 completing one or more revolutions for the full stroke of the displacement member.
  • the position sensor 472 may complete multiple revolutions for the full stroke of the displacement member.
  • a series of switches where n is an integer greater than one, may be employed alone or in combination with a gear reduction to provide a unique position signal for more than one revolution of the position sensor 472. The state of the switches are fed back to the
  • the microcontroller 461 that applies logic to determine a unique position signal corresponding to the longitudinal linear displacement di + d 2 + ... d n of the displacement member.
  • the output of the position sensor 472 is provided to the microcontroller 461 .
  • the position sensor 472 of the sensor arrangement may comprise a magnetic sensor, an analog rotary sensor like a potentiometer, or an array of analog Hall-effect elements, which output a unique combination of position signals or values.
  • the position sensor 472 may comprise any number of magnetic sensing elements, such as, for example, magnetic sensors classified according to whether they measure the total magnetic field or the vector components of the magnetic field.
  • magnetic sensing elements such as, for example, magnetic sensors classified according to whether they measure the total magnetic field or the vector components of the magnetic field.
  • the techniques used to produce both types of magnetic sensors encompass many aspects of physics and electronics.
  • the technologies used for magnetic field sensing include search coil, fluxgate, optically pumped, nuclear precession, SQUID, Hall-effect, anisotropic magnetoresistance, giant
  • magnetostrictive/piezoelectric composites magnetostrictive/piezoelectric composites, magnetodiode, magnetotransistor, fiber-optic, magneto-optic, and microelectromechanical systems-based magnetic sensors, among others.
  • the position sensor 472 for the tracking system 480 comprising an absolute positioning system comprises a magnetic rotary absolute positioning system.
  • the position sensor 472 may be implemented as an AS5055EQFT single-chip magnetic rotary position sensor available from Austria Microsystems, AG.
  • the position sensor 472 is interfaced with the microcontroller 461 to provide an absolute positioning system.
  • the position sensor 472 is a low-voltage and low-power component and includes four Hall-effect elements in an area of the position sensor 472 that is located above a magnet.
  • a high-resolution ADC and a smart power management controller are also provided on the chip.
  • a coordinate rotation digital computer (CORDIC) processor also known as the digit-by-digit method and Volder’s algorithm, is provided to implement a simple and efficient algorithm to calculate hyperbolic and
  • the angle position, alarm bits, and magnetic field information are transmitted over a standard serial communication interface, such as a serial peripheral interface (SPI) interface, to the microcontroller 461 .
  • SPI serial peripheral interface
  • the position sensor 472 provides 12 or 14 bits of resolution.
  • the position sensor 472 may be an AS5055 chip provided in a small QFN 16-pin 4x4x0.85mm package.
  • the tracking system 480 comprising an absolute positioning system may comprise and/or be programmed to implement a feedback controller, such as a PID, state feedback, and adaptive controller.
  • a power source converts the signal from the feedback controller into a physical input to the system: in this case the voltage.
  • Other examples include a PWM of the voltage, current, and force.
  • Other sensor(s) may be provided to measure physical parameters of the physical system in addition to the position measured by the position sensor 472.
  • the other sensor(s) can include sensor arrangements such as those described in U.S. Patent No.
  • an absolute positioning system is coupled to a digital data acquisition system where the output of the absolute positioning system will have a finite resolution and sampling frequency.
  • the absolute positioning system may comprise a compare-and-combine circuit to combine a computed response with a measured response using algorithms, such as a weighted average and a theoretical control loop, that drive the computed response towards the measured response.
  • the computed response of the physical system takes into account properties like mass, inertia, viscous friction, inductance resistance, etc., to predict what the states and outputs of the physical system will be by knowing the input.
  • the absolute positioning system provides an absolute position of the displacement member upon power-up of the instrument, without retracting or advancing the displacement member to a reset (zero or home) position as may be required with conventional rotary encoders that merely count the number of steps forwards or backwards that the motor 482 has taken to infer the position of a device actuator, drive bar, knife, or the like.
  • a sensor 474 such as, for example, a strain gauge or a micro-strain gauge, is configured to measure one or more parameters of the end effector, such as, for example, the amplitude of the strain exerted on the anvil during a clamping operation, which can be indicative of the closure forces applied to the anvil.
  • the measured strain is converted to a digital signal and provided to the processor 462.
  • a sensor 476 such as, for example, a load sensor, can measure the closure force applied by the closure drive system to the anvil in a stapler or a clamp arm in an ultrasonic or electrosurgical instrument.
  • the sensor 476 such as, for example, a load sensor, can measure the firing force applied to a closure member coupled to a clamp arm of the surgical instrument or tool or the force applied by a clamp arm to tissue located in the jaws of an ultrasonic or electrosurgical instrument.
  • a current sensor 478 can be employed to measure the current drawn by the motor 482.
  • the displacement member also may be configured to engage a clamp arm to open or close the clamp arm.
  • the force sensor may be configured to measure the clamping force on tissue. The force required to advance the displacement member can correspond to the current drawn by the motor 482, for example. The measured force is converted to a digital signal and provided to the processor 462.
  • the strain gauge sensor 474 can be used to measure the force applied to the tissue by the end effector.
  • a strain gauge can be coupled to the end effector to measure the force on the tissue being treated by the end effector.
  • a system for measuring forces applied to the tissue grasped by the end effector comprises a strain gauge sensor 474, such as, for example, a micro-strain gauge, that is configured to measure one or more parameters of the end effector, for example.
  • the strain gauge sensor 474 can measure the amplitude or magnitude of the strain exerted on a jaw member of an end effector during a clamping operation, which can be indicative of the tissue compression. The measured strain is converted to a digital signal and provided to a processor 462 of the microcontroller 461 .
  • a load sensor 476 can measure the force used to operate the knife element, for example, to cut the tissue captured between the anvil and the staple cartridge.
  • a load sensor 476 can measure the force used to operate the clamp arm element, for example, to capture tissue between the clamp arm and an ultrasonic blade or to capture tissue between the clamp arm and a jaw of an electrosurgical instrument.
  • a magnetic field sensor can be employed to measure the thickness of the captured tissue. The measurement of the magnetic field sensor also may be converted to a digital signal and provided to the processor 462.
  • a memory 468 may store a technique, an equation, and/or a lookup table which can be employed by the microcontroller 461 in the assessment.
  • the control system 470 of the surgical instrument or tool also may comprise wired or wireless communication circuits to communicate with the modular communication hub as shown in FIGS. 8-1 1 .
  • FIG. 13 illustrates a control circuit 500 configured to control aspects of the surgical instrument or tool according to one aspect of this disclosure.
  • the control circuit 500 can be configured to implement various processes described herein.
  • the control circuit 500 may comprise a microcontroller comprising one or more processors 502 (e.g., microprocessor, microcontroller) coupled to at least one memory circuit 504.
  • the memory circuit 504 stores machine-executable instructions that, when executed by the processor 502, cause the processor 502 to execute machine instructions to implement various processes described herein.
  • the processor 502 may be any one of a number of single-core or multicore processors known in the art.
  • the memory circuit 504 may comprise volatile and non-volatile storage media.
  • the processor 502 may include an instruction processing unit 506 and an arithmetic unit 508.
  • the instruction processing unit may be configured to receive instructions from the memory circuit 504 of this disclosure.
  • FIG. 14 illustrates a combinational logic circuit 510 configured to control aspects of the surgical instrument or tool according to one aspect of this disclosure.
  • the combinational logic circuit 510 can be configured to implement various processes described herein.
  • combinational logic circuit 510 may comprise a finite state machine comprising a combinational logic 512 configured to receive data associated with the surgical instrument or tool at an input 514, process the data by the combinational logic 512, and provide an output 516.
  • FIG. 15 illustrates a sequential logic circuit 520 configured to control aspects of the surgical instrument or tool according to one aspect of this disclosure.
  • the sequential logic circuit 520 or the combinational logic 522 can be configured to implement various processes described herein.
  • the sequential logic circuit 520 may comprise a finite state machine.
  • the sequential logic circuit 520 may comprise a combinational logic 522, at least one memory circuit 524, and a clock 529, for example.
  • the at least one memory circuit 524 can store a current state of the finite state machine.
  • the sequential logic circuit 520 may be synchronous or asynchronous.
  • the combinational logic 522 is configured to receive data associated with the surgical instrument or tool from an input 526, process the data by the combinational logic 522, and provide an output 528.
  • the circuit may comprise a combination of a processor (e.g., processor 502, FIG. 13) and a finite state machine to implement various processes herein.
  • the finite state machine may comprise a combination of a combinational logic circuit (e.g., combinational logic circuit 510, FIG. 14) and the sequential logic circuit 520.
  • FIG. 16 illustrates a surgical instrument or tool comprising a plurality of motors which can be activated to perform various functions.
  • a first motor can be activated to perform a first function
  • a second motor can be activated to perform a second function
  • a third motor can be activated to perform a third function
  • a fourth motor can be activated to perform a fourth function, and so on.
  • the plurality of motors of robotic surgical instrument 600 can be individually activated to cause firing, closure, and/or articulation motions in the end effector. The firing, closure, and/or articulation motions can be transmitted to the end effector through a shaft assembly, for example.
  • the surgical instrument system or tool may include a firing motor 602.
  • the firing motor 602 may be operably coupled to a firing motor drive assembly 604 which can be configured to transmit firing motions, generated by the motor 602 to the end effector, in particular to displace the clamp arm closure member.
  • the closure member may be retracted by reversing the direction of the motor 602, which also causes the clamp arm to open.
  • the surgical instrument or tool may include a closure motor 603.
  • the closure motor 603 may be operably coupled to a closure motor drive assembly 605 which can be configured to transmit closure motions, generated by the motor 603 to the end effector, in particular to displace a closure tube to close the anvil and compress tissue between the anvil and the staple cartridge.
  • the closure motor 603 may be operably coupled to a closure motor drive assembly 605 which can be configured to transmit closure motions, generated by the motor 603 to the end effector, in particular to displace a closure tube to close the clamp arm and compress tissue between the clamp arm and either an ultrasonic blade or jaw member of an electrosurgical device.
  • the closure motions may cause the end effector to transition from an open configuration to an approximated configuration to capture tissue, for example.
  • the end effector may be transitioned to an open position by reversing the direction of the motor 603.
  • the surgical instrument or tool may include one or more articulation motors 606a, 606b, for example.
  • the motors 606a, 606b may be operably coupled to respective articulation motor drive assemblies 608a, 608b, which can be configured to transmit articulation motions generated by the motors 606a, 606b to the end effector.
  • the articulation motions may cause the end effector to articulate relative to the shaft, for example.
  • the surgical instrument or tool may include a plurality of motors which may be configured to perform various independent functions.
  • the plurality of motors of the surgical instrument or tool can be individually or separately activated to perform one or more functions while the other motors remain inactive.
  • the articulation motors 606a, 606b can be activated to cause the end effector to be articulated while the firing motor 602 remains inactive.
  • the firing motor 602 can be activated to fire the plurality of staples, and/or to advance the cutting edge, while the articulation motor 606 remains inactive.
  • the closure motor 603 may be activated simultaneously with the firing motor 602 to cause the closure tube or closure member to advance distally as described in more detail hereinbelow.
  • the surgical instrument or tool may include a common control module 610 which can be employed with a plurality of motors of the surgical instrument or tool.
  • the common control module 610 may accommodate one of the plurality of motors at a time.
  • the common control module 610 can be couplable to and separable from the plurality of motors of the robotic surgical instrument individually.
  • a plurality of the motors of the surgical instrument or tool may share one or more common control modules such as the common control module 610.
  • a plurality of motors of the surgical instrument or tool can be individually and selectively engaged with the common control module 610.
  • the common control module 610 can be selectively switched from interfacing with one of a plurality of motors of the surgical instrument or tool to interfacing with another one of the plurality of motors of the surgical instrument or tool.
  • the common control module 610 can be selectively switched between operable engagement with the articulation motors 606a, 606b and operable
  • a switch 614 can be moved or transitioned between a plurality of positions and/or states. In a first position 616, the switch 614 may electrically couple the common control module 610 to the firing motor 602; in a second position 617, the switch 614 may electrically couple the common control module 610 to the closure motor 603; in a third position 618a, the switch 614 may electrically couple the common control module 610 to the first articulation motor 606a; and in a fourth position 618b, the switch 614 may electrically couple the common control module 610 to the second articulation motor 606b, for example.
  • separate common control modules 610 can be electrically coupled to the firing motor 602, the closure motor 603, and the articulations motor 606a, 606b at the same time.
  • the switch 614 may be a mechanical switch, an electromechanical switch, a solid- state switch, or any suitable switching mechanism.
  • Each of the motors 602, 603, 606a, 606b may comprise a torque sensor to measure the output torque on the shaft of the motor.
  • the force on an end effector may be sensed in any conventional manner, such as by force sensors on the outer sides of the jaws or by a torque sensor for the motor actuating the jaws.
  • the common control module 610 may comprise a motor driver 626 which may comprise one or more H-Bridge FETs.
  • the motor driver 626 may modulate the power transmitted from a power source 628 to a motor coupled to the common control module 610 based on input from a microcontroller 620 (the“controller”), for example.
  • the microcontroller 620 can be employed to determine the current drawn by the motor, for example, while the motor is coupled to the common control module 610, as described above.
  • the microcontroller 620 may include a microprocessor 622 (the “processor”) and one or more non-transitory computer-readable mediums or memory units 624 (the“memory”).
  • the memory 624 may store various program instructions, which when executed may cause the processor 622 to perform a plurality of functions and/or calculations described herein.
  • one or more of the memory units 624 may be coupled to the processor 622, for example.
  • the microcontroller 620 may communicate over a wired or wireless channel, or combinations thereof.
  • the power source 628 can be employed to supply power to the microcontroller 620, for example.
  • the power source 628 may comprise a battery (or“battery pack” or“power pack”), such as a lithium-ion battery, for example.
  • the battery pack may be configured to be releasably mounted to a handle for supplying power to the surgical instrument 600.
  • a number of battery cells connected in series may be used as the power source 628.
  • the power source 628 may be replaceable and/or rechargeable, for example.
  • the processor 622 may control the motor driver 626 to control the position, direction of rotation, and/or velocity of a motor that is coupled to the common control module 610. In certain instances, the processor 622 can signal the motor driver 626 to stop and/or disable a motor that is coupled to the common control module 610.
  • the term“processor” as used herein includes any suitable microprocessor, microcontroller, or other basic computing device that incorporates the functions of a computer’s central processing unit (CPU) on an integrated circuit or, at most, a few integrated circuits.
  • the processor 622 is a multipurpose, programmable device that accepts digital data as input, processes it according to instructions stored in its memory, and provides results as output. It is an example of sequential digital logic, as it has internal memory. Processors operate on numbers and symbols represented in the binary numeral system.
  • the processor 622 may be any single-core or multicore processor such as those known under the trade name ARM Cortex by Texas Instruments.
  • the microcontroller 620 may be an LM 4F230H5QR, available from Texas Instruments, for example.
  • the Texas Instruments LM4F230H5QR is an ARM Cortex- M4F Processor Core comprising an on-chip memory of 256 KB single-cycle flash memory, or other non-volatile memory, up to 40 MHz, a prefetch buffer to improve performance above 40 MHz, a 32 KB single-cycle SRAM, an internal ROM loaded with StellarisWare® software, a 2 KB EEPROM, one or more PWM modules, one or more QEI analogs, one or more 12-bit ADCs with 12 analog input channels, among other features that are readily available for the product datasheet.
  • Other microcontrollers may be readily substituted for use with the module 4410. Accordingly, the present disclosure should not be limited in this context.
  • the memory 624 may include program instructions for controlling each of the motors of the surgical instrument 600 that are couplable to the common control module 610.
  • the memory 624 may include program instructions for controlling the firing motor 602, the closure motor 603, and the articulation motors 606a, 606b.
  • Such program instructions may cause the processor 622 to control the firing, closure, and articulation functions in accordance with inputs from algorithms or control programs of the surgical instrument or tool.
  • one or more mechanisms and/or sensors such as, for example, sensors 630 can be employed to alert the processor 622 to the program instructions that should be used in a particular setting.
  • the sensors 630 may alert the processor 622 to use the program instructions associated with firing, closing, and articulating the end effector.
  • the sensors 630 may comprise position sensors which can be employed to sense the position of the switch 614, for example.
  • the processor 622 may use the program instructions associated with firing the closure member coupled to the clamp arm of the end effector upon detecting, through the sensors 630 for example, that the switch 614 is in the first position 616; the processor 622 may use the program instructions associated with closing the anvil upon detecting, through the sensors 630 for example, that the switch 614 is in the second position 617; and the processor 622 may use the program instructions associated with articulating the end effector upon detecting, through the sensors 630 for example, that the switch 614 is in the third or fourth position 618a, 618b.
  • FIG. 17 is a schematic diagram of a robotic surgical instrument 700 configured to operate a surgical tool described herein according to one aspect of this disclosure.
  • the robotic surgical instrument 700 may be programmed or configured to control distal/proximal translation of a displacement member, distal/proximal displacement of a closure tube, shaft rotation, and articulation, either with single or multiple articulation drive links.
  • the surgical instrument 700 may be programmed or configured to individually control a firing member, a closure member, a shaft member, or one or more articulation members, or combinations thereof.
  • the surgical instrument 700 comprises a control circuit 710 configured to control motor- driven firing members, closure members, shaft members, or one or more articulation members, or combinations thereof.
  • the robotic surgical instrument 700 comprises a control circuit 710 configured to control a clamp arm 716 and a closure member 714 portion of an end effector 702, an ultrasonic blade 718 coupled to an ultrasonic transducer 719 excited by an ultrasonic generator 721 , a shaft 740, and one or more articulation members 742a, 742b via a plurality of motors 704a-704e.
  • a position sensor 734 may be configured to provide position feedback of the closure member 714 to the control circuit 710.
  • Other sensors 738 may be configured to provide feedback to the control circuit 710.
  • a timer/counter 731 provides timing and counting information to the control circuit 710.
  • An energy source 712 may be provided to operate the motors 704a- 704e, and a current sensor 736 provides motor current feedback to the control circuit 710.
  • the motors 704a-704e can be operated individually by the control circuit 710 in an open-loop or closed-loop feedback control.
  • control circuit 710 may comprise one or more microcontrollers, microprocessors, or other suitable processors for executing instructions that cause the processor or processors to perform one or more tasks.
  • a timer/counter 731 provides an output signal, such as the elapsed time or a digital count, to the control circuit 710 to correlate the position of the closure member 714 as determined by the position sensor 734 with the output of the timer/counter 731 such that the control circuit 710 can determine the position of the closure member 714 at a specific time (t) relative to a starting position or the time (t) when the closure member 714 is at a specific position relative to a starting position.
  • the timer/counter 731 may be configured to measure elapsed time, count external events, or time external events.
  • the control circuit 710 may be programmed to control functions of the end effector 702 based on one or more tissue conditions.
  • the control circuit 710 may be programmed to sense tissue conditions, such as thickness, either directly or indirectly, as described herein.
  • the control circuit 710 may be programmed to select a firing control program or closure control program based on tissue conditions.
  • a firing control program may describe the distal motion of the displacement member. Different firing control programs may be selected to better treat different tissue conditions. For example, when thicker tissue is present, the control circuit 710 may be programmed to translate the displacement member at a lower velocity and/or with lower power. When thinner tissue is present, the control circuit 710 may be programmed to translate the displacement member at a higher velocity and/or with higher power.
  • a closure control program may control the closure force applied to the tissue by the clamp arm 716. Other control programs control the rotation of the shaft 740 and the articulation members 742a, 742b.
  • control circuit 710 may generate motor set point signals.
  • the motor set point signals may be provided to various motor controllers 708a-708e.
  • the motor controllers 708a-708e may comprise one or more circuits configured to provide motor drive signals to the motors 704a-704e to drive the motors 704a-704e as described herein.
  • the motors 704a-704e may be brushed DC electric motors.
  • the velocity of the motors 704a-704e may be proportional to the respective motor drive signals.
  • the motors 704a-704e may be brushless DC electric motors, and the respective motor drive signals may comprise a PWM signal provided to one or more stator windings of the motors 704a-704e. Also, in some examples, the motor controllers 708a-708e may be omitted and the control circuit 710 may generate the motor drive signals directly.
  • control circuit 710 may initially operate each of the motors 704a- 704e in an open-loop configuration for a first open-loop portion of a stroke of the displacement member. Based on the response of the robotic surgical instrument 700 during the open-loop portion of the stroke, the control circuit 710 may select a firing control program in a closed-loop configuration.
  • the response of the instrument may include a translation distance of the displacement member during the open-loop portion, a time elapsed during the open-loop portion, the energy provided to one of the motors 704a-704e during the open-loop portion, a sum of pulse widths of a motor drive signal, etc.
  • the control circuit 710 may implement the selected firing control program for a second portion of the displacement member stroke. For example, during a closed-loop portion of the stroke, the control circuit 710 may modulate one of the motors 704a-704e based on translation data describing a position of the displacement member in a closed-loop manner to translate the displacement member at a constant velocity.
  • the motors 704a-704e may receive power from an energy source 712.
  • the energy source 712 may be a DC power supply driven by a main alternating current power source, a battery, a super capacitor, or any other suitable energy source.
  • the motors 704a- 704e may be mechanically coupled to individual movable mechanical elements such as the closure member 714, clamp arm 716, shaft 740, articulation 742a, and articulation 742b via respective transmissions 706a-706e.
  • the transmissions 706a-706e may include one or more gears or other linkage components to couple the motors 704a-704e to movable mechanical elements.
  • a position sensor 734 may sense a position of the closure member 714.
  • the position sensor 734 may be or include any type of sensor that is capable of generating position data that indicate a position of the closure member 714.
  • the position sensor 734 may include an encoder configured to provide a series of pulses to the control circuit 710 as the closure member 714 translates distally and proximally.
  • the control circuit 710 may track the pulses to determine the position of the closure member 714.
  • Other suitable position sensors may be used, including, for example, a proximity sensor.
  • Other types of position sensors may provide other signals indicating motion of the closure member 714.
  • the position sensor 734 may be omitted.
  • the control circuit 710 may track the position of the closure member 714 by aggregating the number and direction of steps that the motor 704 has been instructed to execute.
  • the position sensor 734 may be located in the end effector 702 or at any other portion of the instrument.
  • the outputs of each of the motors 704a-704e include a torque sensor 744a-744e to sense force and have an encoder to sense rotation of the drive shaft.
  • control circuit 710 is configured to drive a firing member such as the closure member 714 portion of the end effector 702.
  • the control circuit 710 provides a motor set point to a motor control 708a, which provides a drive signal to the motor 704a.
  • the output shaft of the motor 704a is coupled to a torque sensor 744a.
  • the torque sensor 744a is coupled to a transmission 706a which is coupled to the closure member 714.
  • the transmission 706a comprises movable mechanical elements such as rotating elements and a firing member to control the movement of the closure member 714 distally and proximally along a longitudinal axis of the end effector 702.
  • the motor 704a may be coupled to the knife gear assembly, which includes a knife gear reduction set that includes a first knife drive gear and a second knife drive gear.
  • a torque sensor 744a provides a firing force feedback signal to the control circuit 710.
  • the firing force signal represents the force required to fire or displace the closure member 714.
  • a position sensor 734 may be configured to provide the position of the closure member 714 along the firing stroke or the position of the firing member as a feedback signal to the control circuit 710.
  • the end effector 702 may include additional sensors 738 configured to provide feedback signals to the control circuit 710. When ready to use, the control circuit 710 may provide a firing signal to the motor control 708a.
  • the motor 704a may drive the firing member distally along the longitudinal axis of the end effector 702 from a proximal stroke start position to a stroke end position distal to the stroke start position.
  • the clamp arm 716 closes towards the ultrasonic blade 718.
  • control circuit 710 is configured to drive a closure member such as the clamp arm 716 portion of the end effector 702.
  • the control circuit 710 provides a motor set point to a motor control 708b, which provides a drive signal to the motor 704b.
  • the output shaft of the motor 704b is coupled to a torque sensor 744b.
  • the torque sensor 744b is coupled to a transmission 706b which is coupled to the clamp arm 716.
  • the transmission 706b comprises movable mechanical elements such as rotating elements and a closure member to control the movement of the clamp arm 716 from the open and closed positions.
  • the motor 704b is coupled to a closure gear assembly, which includes a closure reduction gear set that is supported in meshing engagement with the closure spur gear.
  • the torque sensor 744b provides a closure force feedback signal to the control circuit 710.
  • the closure force feedback signal represents the closure force applied to the clamp arm 716.
  • the position sensor 734 may be configured to provide the position of the closure member as a feedback signal to the control circuit 710. Additional sensors 738 in the end effector 702 may provide the closure force feedback signal to the control circuit 710.
  • the pivotable clamp arm 716 is positioned opposite the ultrasonic blade 718.
  • the control circuit 710 may provide a closure signal to the motor control 708b.
  • the motor 704b advances a closure member to grasp tissue between the clamp arm 716 and the ultrasonic blade 718.
  • control circuit 710 is configured to rotate a shaft member such as the shaft 740 to rotate the end effector 702.
  • the control circuit 710 provides a motor set point to a motor control 708c, which provides a drive signal to the motor 704c.
  • the output shaft of the motor 704c is coupled to a torque sensor 744c.
  • the torque sensor 744c is coupled to a transmission 706c which is coupled to the shaft 740.
  • the transmission 706c comprises movable mechanical elements such as rotating elements to control the rotation of the shaft 740 clockwise or counterclockwise up to and over 360°.
  • the motor 704c is coupled to the rotational transmission assembly, which includes a tube gear segment that is formed on (or attached to) the proximal end of the proximal closure tube for operable engagement by a rotational gear assembly that is operably supported on the tool mounting plate.
  • the torque sensor 744c provides a rotation force feedback signal to the control circuit 710.
  • the rotation force feedback signal represents the rotation force applied to the shaft 740.
  • the position sensor 734 may be configured to provide the position of the closure member as a feedback signal to the control circuit 710. Additional sensors 738 such as a shaft encoder may provide the rotational position of the shaft 740 to the control circuit 710.
  • control circuit 710 is configured to articulate the end effector 702.
  • the control circuit 710 provides a motor set point to a motor control 708d, which provides a drive signal to the motor 704d.
  • the output shaft of the motor 704d is coupled to a torque sensor 744d.
  • the torque sensor 744d is coupled to a transmission 706d which is coupled to an articulation member 742a.
  • the transmission 706d comprises movable mechanical elements such as articulation elements to control the articulation of the end effector 702 ⁇ 65°.
  • the motor 704d is coupled to an articulation nut, which is rotatably journaled on the proximal end portion of the distal spine portion and is rotatably driven thereon by an articulation gear assembly.
  • the torque sensor 744d provides an articulation force feedback signal to the control circuit 710.
  • the articulation force feedback signal represents the articulation force applied to the end effector 702.
  • Sensors 738 such as an articulation encoder, may provide the articulation position of the end effector 702 to the control circuit 710.
  • the articulation function of the robotic surgical system 700 may comprise two articulation members, or links, 742a, 742b. These articulation members 742a,
  • each of articulation links 742a, 742b are driven by separate disks on the robot interface (the rack) which are driven by the two motors 708d, 708e.
  • each of articulation links 742a, 742b can be antagonistically driven with respect to the other link in order to provide a resistive holding motion and a load to the head when it is not moving and to provide an articulation motion as the head is articulated.
  • the articulation members 742a, 742b attach to the head at a fixed radius as the head is rotated. Accordingly, the mechanical advantage of the push-and-pull link changes as the head is rotated. This change in the mechanical advantage may be more pronounced with other articulation link drive systems.
  • the one or more motors 704a-704e may comprise a brushed DC motor with a gearbox and mechanical links to a firing member, closure member, or articulation member.
  • Another example includes electric motors 704a-704e that operate the movable mechanical elements such as the displacement member, articulation links, closure tube, and shaft.
  • An outside influence is an unmeasured, unpredictable influence of things like tissue, surrounding bodies, and friction on the physical system. Such outside influence can be referred to as drag, which acts in opposition to one of electric motors 704a-704e.
  • the outside influence, such as drag may cause the operation of the physical system to deviate from a desired operation of the physical system.
  • the position sensor 734 may be implemented as an absolute positioning system.
  • the position sensor 734 may comprise a magnetic rotary absolute positioning system implemented as an AS5055EQFT single-chip magnetic rotary position sensor available from Austria Microsystems, AG.
  • the position sensor 734 may interface with the control circuit 710 to provide an absolute positioning system.
  • the position may include multiple Hall-effect elements located above a magnet and coupled to a CORDIC processor, also known as the digit-by-digit method and Volder’s algorithm, that is provided to implement a simple and efficient algorithm to calculate hyperbolic and trigonometric functions that require only addition, subtraction, bitshift, and table lookup operations.
  • CORDIC processor also known as the digit-by-digit method and Volder’s algorithm
  • the control circuit 710 may be in communication with one or more sensors 738.
  • the sensors 738 may be positioned on the end effector 702 and adapted to operate with the robotic surgical instrument 700 to measure the various derived parameters such as the gap distance versus time, tissue compression versus time, and anvil strain versus time.
  • the sensors 738 may comprise a magnetic sensor, a magnetic field sensor, a strain gauge, a load cell, a pressure sensor, a force sensor, a torque sensor, an inductive sensor such as an eddy current sensor, a resistive sensor, a capacitive sensor, an optical sensor, and/or any other suitable sensor for measuring one or more parameters of the end effector 702.
  • the sensors 738 may include one or more sensors.
  • the sensors 738 may be located on the clamp arm 716 to determine tissue location using segmented electrodes.
  • the torque sensors 744a- 744e may be configured to sense force such as firing force, closure force, and/or articulation force, among others. Accordingly, the control circuit 710 can sense (1 ) the closure load experienced by the distal closure tube and its position, (2) the firing member at the rack and its position, (3) what portion of the ultrasonic blade 718 has tissue on it, and (4) the load and position on both articulation rods.
  • the one or more sensors 738 may comprise a strain gauge, such as a micro-strain gauge, configured to measure the magnitude of the strain in the clamp arm 716 during a clamped condition.
  • the strain gauge provides an electrical signal whose amplitude varies with the magnitude of the strain.
  • the sensors 738 may comprise a pressure sensor configured to detect a pressure generated by the presence of compressed tissue between the clamp arm 716 and the ultrasonic blade 718.
  • the sensors 738 may be configured to detect impedance of a tissue section located between the clamp arm 716 and the ultrasonic blade 718 that is indicative of the thickness and/or fullness of tissue located therebetween.
  • the sensors 738 may be implemented as one or more limit switches, electromechanical devices, solid-state switches, Hall-effect devices, magneto-resistive (MR) devices, giant magneto-resistive (GMR) devices, magnetometers, among others.
  • the sensors 738 may be implemented as solid-state switches that operate under the influence of light, such as optical sensors, IR sensors, ultraviolet sensors, among others.
  • the switches may be solid-state devices such as transistors (e.g., FET, junction FET, MOSFET, bipolar, and the like).
  • the sensors 738 may include electrical conductorless switches, ultrasonic switches, accelerometers, and inertial sensors, among others.
  • the sensors 738 may be configured to measure forces exerted on the clamp arm 716 by the closure drive system.
  • one or more sensors 738 can be at an interaction point between the closure tube and the clamp arm 716 to detect the closure forces applied by the closure tube to the clamp arm 716.
  • the forces exerted on the clamp arm 716 can be representative of the tissue compression experienced by the tissue section captured between the clamp arm 716 and the ultrasonic blade 718.
  • the one or more sensors 738 can be positioned at various interaction points along the closure drive system to detect the closure forces applied to the clamp arm 716 by the closure drive system.
  • the one or more sensors 738 may be sampled in real time during a clamping operation by the processor of the control circuit 710.
  • the control circuit 710 receives real-time sample measurements to provide and analyze time-based information and assess, in real time, closure forces applied to the clamp arm 716.
  • a current sensor 736 can be employed to measure the current drawn by each of the motors 704a-704e.
  • the force required to advance any of the movable mechanical elements such as the closure member 714 corresponds to the current drawn by one of the motors 704a-704e.
  • the force is converted to a digital signal and provided to the control circuit 710.
  • the control circuit 710 can be configured to simulate the response of the actual system of the instrument in the software of the controller.
  • a displacement member can be actuated to move the closure member 714 in the end effector 702 at or near a target velocity.
  • the robotic surgical instrument 700 can include a feedback controller, which can be one of any feedback controllers, including, but not limited to a PID, a state feedback, a linear-quadratic (LQR), and/or an adaptive controller, for example.
  • the robotic surgical instrument 700 can include a power source to convert the signal from the feedback controller into a physical input such as case voltage, PWM voltage, frequency modulated voltage, current, torque, and/or force, for example. Additional details are disclosed in U.S. Patent Application Serial No. 15/636,829, titled CLOSED LOOP VELOCITY CONTROL TECHNIQUES FOR ROBOTIC SURGICAL INSTRUMENT, filed June 29, 2017, which is herein incorporated by reference in its entirety.
  • FIG. 18 illustrates a schematic diagram of a surgical instrument 750 configured to control the distal translation of a displacement member according to one aspect of this disclosure.
  • the surgical instrument 750 is programmed to control the distal translation of a displacement member such as the closure member 764.
  • the surgical instrument 750 comprises an end effector 752 that may comprise a clamp arm 766, a closure member 764, and an ultrasonic blade 768 coupled to an ultrasonic transducer 769 driven by an ultrasonic generator 771 .
  • the position, movement, displacement, and/or translation of a linear displacement member can be measured by an absolute positioning system, sensor arrangement, and position sensor 784. Because the closure member 764 is coupled to a longitudinally movable drive member, the position of the closure member 764 can be determined by measuring the position of the longitudinally movable drive member employing the position sensor 784. Accordingly, in the following description, the position, displacement, and/or translation of the closure member 764 can be achieved by the position sensor 784 as described herein.
  • a control circuit 760 may be programmed to control the translation of the displacement member, such as the closure member 764.
  • the control circuit 760 may comprise one or more microcontrollers, microprocessors, or other suitable processors for executing instructions that cause the processor or processors to control the displacement member, e.g., the closure member 764, in the manner described.
  • a timer/counter 781 provides an output signal, such as the elapsed time or a digital count, to the control circuit 760 to correlate the position of the closure member 764 as determined by the position sensor 784 with the output of the timer/counter 781 such that the control circuit 760 can determine the position of the closure member 764 at a specific time (t) relative to a starting position.
  • the timer/counter 781 may be configured to measure elapsed time, count external events, or time external events.
  • the control circuit 760 may generate a motor set point signal 772.
  • the motor set point signal 772 may be provided to a motor controller 758.
  • the motor controller 758 may comprise one or more circuits configured to provide a motor drive signal 774 to the motor 754 to drive the motor 754 as described herein.
  • the motor 754 may be a brushed DC electric motor.
  • the velocity of the motor 754 may be proportional to the motor drive signal 774.
  • the motor 754 may be a brushless DC electric motor and the motor drive signal 774 may comprise a PWM signal provided to one or more stator windings of the motor 754.
  • the motor controller 758 may be omitted, and the control circuit 760 may generate the motor drive signal 774 directly.
  • the motor 754 may receive power from an energy source 762.
  • the energy source 762 may be or include a battery, a super capacitor, or any other suitable energy source.
  • the motor 754 may be mechanically coupled to the closure member 764 via a transmission 756.
  • the transmission 756 may include one or more gears or other linkage components to couple the motor 754 to the closure member 764.
  • a position sensor 784 may sense a position of the closure member 764.
  • the position sensor 784 may be or include any type of sensor that is capable of generating position data that indicate a position of the closure member 764.
  • the position sensor 784 may include an encoder configured to provide a series of pulses to the control circuit 760 as the closure member 764 translates distally and proximally.
  • the control circuit 760 may track the pulses to determine the position of the closure member 764.
  • Other suitable position sensors may be used, including, for example, a proximity sensor. Other types of position sensors may provide other signals indicating motion of the closure member 764.
  • the position sensor 784 may be omitted.
  • the control circuit 760 may track the position of the closure member 764 by aggregating the number and direction of steps that the motor 754 has been instructed to execute.
  • the position sensor 784 may be located in the end effector 752 or at any other portion of the instrument.
  • the control circuit 760 may be in communication with one or more sensors 788.
  • the sensors 788 may be positioned on the end effector 752 and adapted to operate with the surgical instrument 750 to measure the various derived parameters such as gap distance versus time, tissue compression versus time, and anvil strain versus time.
  • the sensors 788 may comprise a magnetic sensor, a magnetic field sensor, a strain gauge, a pressure sensor, a force sensor, an inductive sensor such as an eddy current sensor, a resistive sensor, a capacitive sensor, an optical sensor, and/or any other suitable sensor for measuring one or more parameters of the end effector 752.
  • the sensors 788 may include one or more sensors.
  • the one or more sensors 788 may comprise a strain gauge, such as a micro-strain gauge, configured to measure the magnitude of the strain in the clamp arm 766 during a clamped condition.
  • the strain gauge provides an electrical signal whose amplitude varies with the magnitude of the strain.
  • the sensors 788 may comprise a pressure sensor configured to detect a pressure generated by the presence of compressed tissue between the clamp arm 766 and the ultrasonic blade 768.
  • the sensors 788 may be configured to detect impedance of a tissue section located between the clamp arm 766 and the ultrasonic blade 768 that is indicative of the thickness and/or fullness of tissue located therebetween.
  • the sensors 788 may be is configured to measure forces exerted on the clamp arm 766 by a closure drive system.
  • one or more sensors 788 can be at an interaction point between a closure tube and the clamp arm 766 to detect the closure forces applied by a closure tube to the clamp arm 766.
  • the forces exerted on the clamp arm 766 can be
  • the one or more sensors 788 can be positioned at various interaction points along the closure drive system to detect the closure forces applied to the clamp arm 766 by the closure drive system.
  • the one or more sensors 788 may be sampled in real time during a clamping operation by a processor of the control circuit 760.
  • the control circuit 760 receives real-time sample measurements to provide and analyze time-based information and assess, in real time, closure forces applied to the clamp arm 766.
  • a current sensor 786 can be employed to measure the current drawn by the motor 754.
  • the force required to advance the closure member 764 corresponds to the current drawn by the motor 754.
  • the force is converted to a digital signal and provided to the control circuit 760.
  • the control circuit 760 can be configured to simulate the response of the actual system of the instrument in the software of the controller.
  • a displacement member can be actuated to move a closure member 764 in the end effector 752 at or near a target velocity.
  • the surgical instrument 750 can include a feedback controller, which can be one of any feedback controllers, including, but not limited to a PID, a state feedback, LQR, and/or an adaptive controller, for example.
  • the surgical instrument 750 can include a power source to convert the signal from the feedback controller into a physical input such as case voltage, PWM voltage, frequency modulated voltage, current, torque, and/or force, for example.
  • the actual drive system of the surgical instrument 750 is configured to drive the displacement member, cutting member, or closure member 764, by a brushed DC motor with gearbox and mechanical links to an articulation and/or knife system.
  • a brushed DC motor with gearbox and mechanical links to an articulation and/or knife system.
  • the electric motor 754 that operates the displacement member and the articulation driver, for example, of an interchangeable shaft assembly.
  • An outside influence is an unmeasured, unpredictable influence of things like tissue, surrounding bodies and friction on the physical system. Such outside influence can be referred to as drag which acts in opposition to the electric motor 754.
  • the outside influence, such as drag may cause the operation of the physical system to deviate from a desired operation of the physical system.
  • a surgical instrument 750 comprising an end effector 752 with motor-driven surgical sealing and cutting implements.
  • a motor 754 may drive a displacement member distally and proximally along a longitudinal axis of the end effector 752.
  • the end effector 752 may comprise a pivotable clamp arm 766 and, when configured for use, an ultrasonic blade 768 positioned opposite the clamp arm 766.
  • a clinician may grasp tissue between the clamp arm 766 and the ultrasonic blade 768, as described herein.
  • the clinician may provide a firing signal, for example by depressing a trigger of the instrument 750.
  • the motor 754 may drive the displacement member distally along the longitudinal axis of the end effector 752 from a proximal stroke begin position to a stroke end position distal of the stroke begin position.
  • the closure member 764 with a cutting element positioned at a distal end may cut the tissue between the ultrasonic blade 768 and the clamp arm 766.
  • the surgical instrument 750 may comprise a control circuit 760 programmed to control the distal translation of the displacement member, such as the closure member 764, for example, based on one or more tissue conditions.
  • the control circuit 760 may be programmed to sense tissue conditions, such as thickness, either directly or indirectly, as described herein.
  • the control circuit 760 may be programmed to select a control program based on tissue conditions.
  • a control program may describe the distal motion of the displacement member. Different control programs may be selected to better treat different tissue conditions. For example, when thicker tissue is present, the control circuit 760 may be programmed to translate the displacement member at a lower velocity and/or with lower power. When thinner tissue is present, the control circuit 760 may be programmed to translate the displacement member at a higher velocity and/or with higher power.
  • the control circuit 760 may initially operate the motor 754 in an open loop configuration for a first open loop portion of a stroke of the displacement member. Based on a response of the instrument 750 during the open loop portion of the stroke, the control circuit 760 may select a firing control program.
  • the response of the instrument may include, a translation distance of the displacement member during the open loop portion, a time elapsed during the open loop portion, energy provided to the motor 754 during the open loop portion, a sum of pulse widths of a motor drive signal, etc.
  • the control circuit 760 may implement the selected firing control program for a second portion of the displacement member stroke.
  • control circuit 760 may modulate the motor 754 based on translation data describing a position of the displacement member in a closed loop manner to translate the displacement member at a constant velocity. Additional details are disclosed in U.S. Patent Application Serial No.
  • FIG. 19 is a schematic diagram of a surgical instrument 790 configured to control various functions according to one aspect of this disclosure.
  • the surgical instrument 790 is programmed to control distal translation of a displacement member such as the closure member 764.
  • the surgical instrument 790 comprises an end effector 792 that may comprise a clamp arm 766, a closure member 764, and an ultrasonic blade 768 which may be interchanged with or work in conjunction with one or more RF electrodes 796 (shown in dashed line).
  • the ultrasonic blade 768 is coupled to an ultrasonic transducer 769 driven by an ultrasonic generator 771 .
  • sensors 788 may be implemented as a limit switch, electromechanical device, solid-state switches, Hall-effect devices, MR devices, GMR devices, magnetometers, among others.
  • the sensors 638 may be solid-state switches that operate under the influence of light, such as optical sensors, IR sensors, ultraviolet sensors, among others.
  • the switches may be solid-state devices such as transistors (e.g., FET, junction FET, MOSFET, bipolar, and the like).
  • the sensors 788 may include electrical conductorless switches, ultrasonic switches, accelerometers, and inertial sensors, among others.
  • the position sensor 784 may be implemented as an absolute positioning system comprising a magnetic rotary absolute positioning system implemented as an
  • the position sensor 784 may interface with the control circuit 760 to provide an absolute positioning system.
  • the position may include multiple Hall-effect elements located above a magnet and coupled to a CORDIC processor, also known as the digit-by-digit method and Volder’s algorithm, that is provided to implement a simple and efficient algorithm to calculate hyperbolic and trigonometric functions that require only addition, subtraction, bitshift, and table lookup operations.
  • CORDIC processor also known as the digit-by-digit method and Volder’s algorithm
  • the position sensor 784 may be omitted.
  • the control circuit 760 may track the position of the closure member 764 by aggregating the number and direction of steps that the motor has been instructed to execute.
  • the position sensor 784 may be located in the end effector 792 or at any other portion of the instrument.
  • the control circuit 760 may be in communication with one or more sensors 788.
  • the sensors 788 may be positioned on the end effector 792 and adapted to operate with the surgical instrument 790 to measure the various derived parameters such as gap distance versus time, tissue compression versus time, and anvil strain versus time.
  • the sensors 788 may comprise a magnetic sensor, a magnetic field sensor, a strain gauge, a pressure sensor, a force sensor, an inductive sensor such as an eddy current sensor, a resistive sensor, a capacitive sensor, an optical sensor, and/or any other suitable sensor for measuring one or more parameters of the end effector 792.
  • the sensors 788 may include one or more sensors.
  • An RF energy source 794 is coupled to the end effector 792 and is applied to the RF electrode 796 when the RF electrode 796 is provided in the end effector 792 in place of the ultrasonic blade 768 or to work in conjunction with the ultrasonic blade 768.
  • the ultrasonic blade is made of electrically conductive metal and may be employed as the return path for electrosurgical RF current.
  • the control circuit 760 controls the delivery of the RF energy to the RF electrode 796.
  • smart ultrasonic energy devices may comprise adaptive algorithms to control the operation of the ultrasonic blade.
  • the ultrasonic blade adaptive control algorithms are configured to identify tissue type and adjust device parameters.
  • the ultrasonic blade control algorithms are configured to parameterize tissue type.
  • An algorithm to detect the collagen/elastic ratio of tissue to tune the amplitude of the distal tip of the ultrasonic blade is described in the following section of the present disclosure.
  • FIGS. 1-85 Various aspects of smart ultrasonic energy devices are described herein in connection with FIGS. 1-85, for example. Accordingly, the following description of adaptive ultrasonic blade control algorithms should be read in conjunction with FIGS. 1-85 and the description associated therewith.
  • adaptive ultrasonic blade control algorithms may be employed to adjust the parameters of the ultrasonic device based on the type of tissue in contact with the ultrasonic blade.
  • the parameters of the ultrasonic device may be adjusted based on the location of the tissue within the jaws of the ultrasonic end effector, for example, the location of the tissue between the clamp arm and the ultrasonic blade.
  • the impedance of the ultrasonic transducer may be employed to differentiate what percentage of the tissue is located in the distal or proximal end of the end effector.
  • the reactions of the ultrasonic device may be based on the tissue type or compressibility of the tissue.
  • the parameters of the ultrasonic device may be adjusted based on the identified tissue type or parameterization.
  • the mechanical displacement amplitude of the distal tip of the ultrasonic blade may be tuned based on the ration of collagen to elastin tissue detected during the tissue identification procedure.
  • the ratio of collagen to elastin tissue may be detected used a variety of techniques including infrared (IR) surface reflectance and emissivity.
  • IR infrared
  • the force applied to the tissue by the clamp arm and/or the stroke of the clamp arm to produce gap and compression. Electrical continuity across a jaw equipped with electrodes may be employed to determine what percentage of the jaw is covered with tissue.
  • the generator module 240 is configured to execute the adaptive ultrasonic blade control algorithm(s) 802 as described herein with reference to FIGS. 43A-54.
  • the device/instrument 235 is configured to execute the adaptive ultrasonic blade control algorithm(s) 804 as described herein with reference to FIGS. 43A-54.
  • both the device/instrument 235 and the device/instrument 235 are configured to execute the adaptive ultrasonic blade control algorithms 802, 804 as described herein with reference to FIGS. 43A-54.
  • the generator module 240 may comprise a patient isolated stage in communication with a non-isolated stage via a power transformer.
  • a secondary winding of the power transformer is contained in the isolated stage and may comprise a tapped configuration (e.g., a center-tapped or a non-center-tapped configuration) to define drive signal outputs for delivering drive signals to different surgical instruments, such as, for example, an ultrasonic surgical instrument, an RF electrosurgical instrument, and a multifunction surgical instrument which includes ultrasonic and RF energy modes that can be delivered alone or simultaneously.
  • the drive signal outputs may output an ultrasonic drive signal (e.g., a 420V root- mean-square (RMS) drive signal) to an ultrasonic surgical instrument 241
  • the drive signal outputs may output an RF electrosurgical drive signal (e.g., a 100V RMS drive signal) to an RF electrosurgical instrument 241 .
  • RMS root- mean-square
  • RF electrosurgical drive signal e.g., a 100V RMS drive signal
  • the generator module 240 or the device/instrument 235 or both are coupled to the modular control tower 236 connected to multiple operating theater devices such as, for example, intelligent surgical instruments, robots, and other computerized devices located in the operating theater, as described with reference to FIGS. 8-1 1 , for example.
  • FIG. 21 illustrates an example of a generator 900, which is one form of a generator configured to couple to an ultrasonic instrument and further configured to execute adaptive ultrasonic blade control algorithms in a surgical data network comprising a modular
  • the generator 900 is configured to deliver multiple energy modalities to a surgical instrument.
  • the generator 900 provides RF and ultrasonic signals for delivering energy to a surgical instrument either independently or simultaneously.
  • the RF and ultrasonic signals may be provided alone or in combination and may be provided simultaneously.
  • at least one generator output can deliver multiple energy modalities (e.g., ultrasonic, bipolar or monopolar RF, irreversible and/or reversible electroporation, and/or microwave energy, among others) through a single port, and these signals can be delivered separately or simultaneously to the end effector to treat tissue.
  • the generator 900 comprises a processor 902 coupled to a waveform generator 904.
  • the processor 902 and waveform generator 904 are configured to generate a variety of signal waveforms based on information stored in a memory coupled to the processor 902, not shown for clarity of disclosure.
  • the digital information associated with a waveform is provided to the waveform generator 904 which includes one or more DAC circuits to convert the digital input into an analog output.
  • the analog output is fed to an amplifier 1 106 for signal conditioning and amplification.
  • the conditioned and amplified output of the amplifier 906 is coupled to a power transformer 908.
  • the signals are coupled across the power transformer 908 to the secondary side, which is in the patient isolation side.
  • a first signal of a first energy modality is provided to the surgical instrument between the terminals labeled ENERGYi and RETURN.
  • a second signal of a second energy modality is coupled across a capacitor 910 and is provided to the surgical instrument between the terminals labeled ENERGY 2 and RETURN.
  • n is a positive integer greater than 1 . It also will be appreciated that up to“n” return paths RETURN n may be provided without departing from the scope of the present disclosure.
  • a first voltage sensing circuit 912 is coupled across the terminals labeled ENERGYi and the RETURN path to measure the output voltage therebetween.
  • a second voltage sensing circuit 924 is coupled across the terminals labeled ENERGY 2 and the RETURN path to measure the output voltage therebetween.
  • a current sensing circuit 914 is disposed in series with the RETURN leg of the secondary side of the power transformer 908 as shown to measure the output current for either energy modality. If different return paths are provided for each energy modality, then a separate current sensing circuit should be provided in each return leg.
  • the outputs of the first and second voltage sensing circuits 912, 924 are provided to respective isolation transformers 916, 922 and the output of the current sensing circuit 914 is provided to another isolation transformer 918.
  • the outputs of the isolation transformers 916, 928, 922 in the on the primary side of the power transformer 908 (non-patient isolated side) are provided to a one or more ADC circuit 926.
  • the digitized output of the ADC circuit 926 is provided to the processor 902 for further processing and computation.
  • the output voltages and output current feedback information can be employed to adjust the output voltage and current provided to the surgical instrument and to compute output impedance, among other parameters.
  • Input/output communications between the processor 902 and patient isolated circuits is provided through an interface circuit 920. Sensors also may be in electrical communication with the processor 902 by way of the interface circuit 920.
  • the impedance may be determined by the processor 902 by dividing the output of either the first voltage sensing circuit 912 coupled across the terminals labeled ENERGYi/RETURN or the second voltage sensing circuit 924 coupled across the terminals labeled ENERGY 2 /RETURN by the output of the current sensing circuit 914 disposed in series with the RETURN leg of the secondary side of the power transformer 908.
  • the outputs of the first and second voltage sensing circuits 912, 924 are provided to separate isolations transformers 916, 922 and the output of the current sensing circuit 914 is provided to another isolation transformer 916.
  • the digitized voltage and current sensing measurements from the ADC circuit 926 are provided the processor 902 for computing impedance.
  • the first energy modality ENERGYi may be ultrasonic energy and the second energy modality ENERGY 2 may be RF energy.
  • other energy modalities include irreversible and/or reversible
  • the ultrasonic transducer impedance may be measured by dividing the output of the first voltage sensing circuit 912 by the current sensing circuit 914 and the tissue impedance may be measured by dividing the output of the second voltage sensing circuit 924 by the current sensing circuit 914.
  • the generator 900 comprising at least one output port can include a power transformer 908 with a single output and with multiple taps to provide power in the form of one or more energy modalities, such as ultrasonic, bipolar or monopolar RF, irreversible and/or reversible electroporation, and/or microwave energy, among others, for example, to the end effector depending on the type of treatment of tissue being performed.
  • the generator 900 can deliver energy with higher voltage and lower current to drive an ultrasonic transducer, with lower voltage and higher current to drive RF electrodes for sealing tissue, or with a coagulation waveform for spot coagulation using either monopolar or bipolar RF electrosurgical electrodes.
  • the output waveform from the generator 900 can be steered, switched, or filtered to provide the frequency to the end effector of the surgical instrument.
  • the connection of an ultrasonic transducer to the generator 900 output would be preferably located between the output labeled ENERGYi and RETURN as shown in FIG. 21.
  • a connection of RF bipolar electrodes to the generator 900 output would be preferably located between the output labeled ENERGY 2 and RETURN.
  • the preferred connections would be active electrode (e.g., pencil or other probe) to the ENERGY 2 output and a suitable return pad connected to the RETURN output.
  • wireless and its derivatives may be used to describe circuits, devices, systems, methods, techniques, communications channels, etc., that may communicate data through the use of modulated electromagnetic radiation through a non-solid medium.
  • the term does not imply that the associated devices do not contain any wires, although in some aspects they might not.
  • the communication module may implement any of a number of wireless or wired communication standards or protocols, including but not limited to Wi-Fi (IEEE 802.1 1 family), WiMAX (IEEE 802.16 family), IEEE 802.20, long term evolution (LTE), Ev-DO, HSPA+, HSDPA+, HSUPA+, EDGE, GSM, GPRS, CDMA, TDMA, DECT, Bluetooth, Ethernet derivatives thereof, as well as any other wireless and wired protocols that are designated as 3G, 4G, 5G, and beyond.
  • the computing module may include a plurality of communication modules.
  • a first communication module may be dedicated to shorter range wireless communications such as Wi-Fi and Bluetooth and a second communication module may be dedicated to longer range wireless communications such as GPS, EDGE, GPRS, CDMA, WiMAX, LTE, Ev-DO, and others.
  • processor or processing unit is an electronic circuit which performs operations on some external data source, usually memory or some other data stream.
  • the term is used herein to refer to the central processor (central processing unit) in a system or computer systems (especially systems on a chip (SoCs)) that combine a number of specialized “processors.”
  • SoC system on a chip or system on chip
  • SOC system on chip
  • IC integrated circuit
  • a SoC integrates a microcontroller (or microprocessor) with advanced peripherals like graphics processing unit (GPU), Wi-Fi module, or coprocessor.
  • a SoC may or may not contain built-in memory.
  • a microcontroller or controller is a system that integrates a
  • a microcontroller may be implemented as a small computer on a single integrated circuit. It may be similar to a SoC; an SoC may include a microcontroller as one of its components.
  • a microcontroller may contain one or more core processing units (CPUs) along with memory and programmable input/output peripherals.
  • Program memory in the form of Ferroelectric RAM,
  • NOR flash or OTP ROM is also often included on chip, as well as a small amount of RAM.
  • Microcontrollers may be employed for embedded applications, in contrast to the
  • microprocessors used in personal computers or other general purpose applications consisting of various discrete chips.
  • controller or microcontroller may be a stand-alone 1C or chip device that interfaces with a peripheral device. This may be a link between two parts of a computer or a controller on an external device that manages the operation of (and connection with) that device.
  • any of the processors or microcontrollers described herein may be implemented by any single core or multicore processor such as those known under the trade name ARM Cortex by Texas Instruments.
  • the processor may be an LM4F230H5QR ARM Cortex- M4F Processor Core, available from Texas Instruments, for example, comprising on-chip memory of 256 KB single-cycle flash memory, or other non-volatile memory, up to 40 MHz, a prefetch buffer to improve performance above 40 MHz, a 32 KB single-cycle serial random access memory (SRAM), internal read-only memory (ROM) loaded with Stel laris Ware® software, 2 KB electrically erasable programmable read-only memory (EEPROM), one or more pulse width modulation (PWM) modules, one or more quadrature encoder inputs (QEI) analog, one or more 12-bit Analog-to-Digital Converters (ADC) with 12 analog input channels, details of which are available for the product datasheet.
  • SRAM serial random access memory
  • the processor may comprise a safety controller comprising two controller-based families such as TMS570 and RM4x known under the trade name Hercules ARM Cortex R4, also by Texas Instruments.
  • the safety controller may be configured specifically for IEC 61508 and ISO 26262 safety critical applications, among others, to provide advanced integrated safety features while delivering scalable performance, connectivity, and memory options.
  • Modular devices include the modules (as described in connection with FIGS. 3 and 9, for example) that are receivable within a surgical hub and the surgical devices or instruments that can be connected to the various modules in order to connect or pair with the corresponding surgical hub.
  • the modular devices include, for example, intelligent surgical instruments, medical imaging devices, suction/irrigation devices, smoke evacuators, energy generators, ventilators, insufflators, and displays.
  • the modular devices described herein can be controlled by control algorithms.
  • the control algorithms can be executed on the modular device itself, on the surgical hub to which the particular modular device is paired, or on both the modular device and the surgical hub (e.g., via a distributed computing architecture).
  • the modular devices’ control algorithms control the devices based on data sensed by the modular device itself (i.e., by sensors in, on, or connected to the modular device). This data can be related to the patient being operated on (e.g., tissue properties or insufflation pressure) or the modular device itself (e.g., the rate at which a knife is being advanced, motor current, or energy levels).
  • a control algorithm for a surgical stapling and cutting instrument can control the rate at which the instrument’s motor drives its knife through tissue according to resistance encountered by the knife as it advances.
  • FIG. 22 illustrates one form of a surgical system 1000 comprising a generator 1 100 and various surgical instruments 1 104, 1 106, 1 108 usable therewith, where the surgical instrument 1 104 is an ultrasonic surgical instrument, the surgical instrument 1 106 is an RF electrosurgical instrument, and the multifunction surgical instrument 1 108 is a combination ultrasonic/RF electrosurgical instrument.
  • the generator 1 100 is configurable for use with a variety of surgical instruments. According to various forms, the generator 1 100 may be configurable for use with different surgical instruments of different types including, for example, ultrasonic surgical instruments 1 104, RF electrosurgical instruments 1 106, and multifunction surgical instruments 1 108 that integrate RF and ultrasonic energies delivered simultaneously from the generator 1 100.
  • the generator 1 100 is shown separate from the surgical instruments 1 104, 1 106, 1 108 in one form, the generator 1 100 may be formed integrally with any of the surgical instruments 1 104, 1 106, 1 108 to form a unitary surgical system.
  • the generator 1 100 comprises an input device 1 1 10 located on a front panel of the generator 1 100 console.
  • the input device 1 1 10 may comprise any suitable device that generates signals suitable for programming the operation of the generator 1 100.
  • the generator 1 100 may be configured for wired or wireless communication.
  • the generator 1 100 is configured to drive multiple surgical instruments 1 104, 1 106, 1 108.
  • the first surgical instrument is an ultrasonic surgical instrument 1 104 and comprises a handpiece 1 105 (HP), an ultrasonic transducer 1 120, a shaft 1 126, and an end effector 1 122.
  • the end effector 1 122 comprises an ultrasonic blade 1 128 acoustically coupled to the ultrasonic transducer 1 120 and a clamp arm 1 140.
  • the handpiece 1 105 comprises a trigger 1 143 to operate the clamp arm 1 140 and a combination of the toggle buttons 1 134a, 1 134b, 1 134c to energize and drive the ultrasonic blade 1 128 or other function.
  • the toggle buttons 1 134a, 1 134b, 1 134c can be configured to energize the ultrasonic transducer 1 120 with the generator 1 100.
  • the generator 1 100 also is configured to drive a second surgical instrument 1 106.
  • the second surgical instrument 1 106 is an RF electrosurgical instrument and comprises a handpiece 1 107 (HP), a shaft 1 127, and an end effector 1 124.
  • the end effector 1 124 comprises electrodes in clamp arms 1 142a, 1 142b and return through an electrical conductor portion of the shaft 1 127.
  • the electrodes are coupled to and energized by a bipolar energy source within the generator 1 100.
  • the handpiece 1 107 comprises a trigger 1 145 to operate the clamp arms 1 142a, 1 142b and an energy button 1 135 to actuate an energy switch to energize the electrodes in the end effector 1 124.
  • the generator 1 100 also is configured to drive a multifunction surgical instrument 1 108.
  • the multifunction surgical instrument 1 108 comprises a handpiece 1 109 (HP), a shaft 1 129, and an end effector 1 125.
  • the end effector 1 125 comprises an ultrasonic blade 1 149 and a clamp arm 1 146.
  • the ultrasonic blade 1 149 is acoustically coupled to the ultrasonic transducer 1 120.
  • the handpiece 1 109 comprises a trigger 1 147 to operate the clamp arm 1 146 and a combination of the toggle buttons 1 137a, 1 137b, 1 137c to energize and drive the ultrasonic blade 1 149 or other function.
  • the toggle buttons 1 137a, 1 137b, 1 137c can be configured to energize the ultrasonic transducer 1 120 with the generator 1 100 and energize the ultrasonic blade 1 149 with a bipolar energy source also contained within the generator 1 100.
  • the generator 1 100 is configurable for use with a variety of surgical instruments. According to various forms, the generator 1 100 may be configurable for use with different surgical instruments of different types including, for example, the ultrasonic surgical instrument 1 104, the RF electrosurgical instrument 1 106, and the multifunction surgical instrument 1 108 that integrates RF and ultrasonic energies delivered simultaneously from the generator 1 100. Although in the form of FIG. 22 the generator 1 100 is shown separate from the surgical instruments 1 104, 1 106, 1 108, in another form the generator 1 100 may be formed integrally with any one of the surgical instruments 1 104, 1 106, 1 108 to form a unitary surgical system.
  • the generator 1 100 comprises an input device 1 1 10 located on a front panel of the generator 1 100 console.
  • the input device 1 1 10 may comprise any suitable device that generates signals suitable for programming the operation of the generator 1 100.
  • the generator 1 100 also may comprise one or more output devices 1 1 12. Further aspects of generators for digitally generating electrical signal waveforms and surgical instruments are described in US patent publication US-2017-0086914-A1 , which is herein incorporated by reference in its entirety.
  • FIG. 23 is an end effector 1 122 of the example ultrasonic device 1 104, in accordance with at least one aspect of the present disclosure.
  • the end effector 1 122 may comprise a blade 1 128 that may be coupled to the ultrasonic transducer 1 120 via a wave guide.
  • the end effector 1 122 may also comprise a clamp arm 1 140 that may be configured for cooperative action with the blade 1 128 of the end effector 1 122.
  • the clamp arm 1 140 may comprise a set of jaws.
  • the clamp arm 1 140 may be pivotally connected at a distal end of a shaft 1 126 of the instrument portion 1 104.
  • the clamp arm 1 140 may include a clamp arm tissue pad 1 163, which may be formed from TEFLON® or other suitable low-friction material.
  • the pad 1 163 may be mounted for cooperation with the blade 1 128, with pivotal movement of the clamp arm 1 140 positioning the clamp pad 1 163 in substantially parallel relationship to, and in contact with, the blade 1 128.
  • the tissue pad 1 163 may be provided with a sawtooth-like configuration including a plurality of axially spaced, proximally extending gripping teeth 1 161 to enhance the gripping of tissue in cooperation with the blade 1 128.
  • the clamp arm 1 140 may transition from the open position shown in FIG. 23 to a closed position (with the clamp arm 1 140 in contact with or proximity to the blade 1 128) in any suitable manner.
  • the handpiece 1 105 may comprise a jaw closure trigger. When actuated by a clinician, the jaw closure trigger may pivot the clamp arm 1 140 in any suitable manner.
  • the generator 1 100 may be activated to provide the drive signal to the ultrasonic transducer 1 120 in any suitable manner.
  • the generator 1 100 may comprise a foot switch 1430 (FIG. 24) coupled to the generator 1 100 via a footswitch cable 1432.
  • a clinician may activate the ultrasonic transducer 1 120, and thereby the ultrasonic transducer 1 120 and blade 1 128, by depressing the foot switch 1430.
  • some aspects of the device 1 104 may utilize one or more switches positioned on the handpiece 1 105 that, when activated, may cause the generator 1 100 to activate the ultrasonic transducer 1 120.
  • the one or more switches may comprise a pair of toggle buttons 1 134a, 1 134b, 1 134c (FIG. 22), for example, to determine an operating mode of the device 1 104.
  • the toggle button 1 134a When the toggle button 1 134a is depressed, for example, the ultrasonic generator 1 100 may provide a maximum drive signal to the ultrasonic transducer 1 120, causing it to produce maximum ultrasonic energy output.
  • Depressing toggle button 1 134b may cause the ultrasonic generator 1 100 to provide a user-selectable drive signal to the ultrasonic transducer 1 120, causing it to produce less than the maximum ultrasonic energy output.
  • the device 1 104 additionally or alternatively may comprise a second switch to, for example, indicate a position of a jaw closure trigger for operating the jaws via the clamp arm 1 140 of the end effector 1 122.
  • the ultrasonic generator 1 100 may be activated based on the position of the jaw closure trigger, (e.g., as the clinician depresses the jaw closure trigger to close the jaws via the clamp arm 1 140, ultrasonic energy may be applied).
  • the one or more switches may comprise a toggle button 1 134c that, when depressed, causes the generator 1 100 to provide a pulsed output (FIG. 22).
  • the pulses may be provided at any suitable frequency and grouping, for example.
  • the power level of the pulses may be the power levels associated with toggle buttons 1 134a, 1 134b (maximum, less than maximum), for example.
  • a device 1 104 may comprise any combination of the toggle buttons 1 134a, 1 134b, 1 134c (FIG. 22).
  • the device 1 104 could be configured to have only two toggle buttons: a toggle button 1 134a for producing maximum ultrasonic energy output and a toggle button 1 134c for producing a pulsed output at either the maximum or less than maximum power level per.
  • the drive signal output configuration of the generator 1 100 could be five continuous signals, or any discrete number of individual pulsed signals (1 , 2, 3, 4, or 5).
  • the specific drive signal configuration may be controlled based upon, for example, EEPROM settings in the generator 1 100 and/or user power level selection(s).
  • a two-position switch may be provided as an alternative to a toggle button 1 134c (FIG. 22).
  • a device 1 104 may include a toggle button 1 134a for producing a continuous output at a maximum power level and a two-position toggle button 1 134b. In a first detented position, toggle button 1 134b may produce a continuous output at a less than maximum power level, and in a second detented position the toggle button 1 134b may produce a pulsed output (e.g., at either a maximum or less than maximum power level, depending upon the EEPROM settings).
  • the RF electrosurgical end effector 1 124, 1 125 may also comprise a pair of electrodes.
  • the electrodes may be in communication with the generator 1 100, for example, via a cable.
  • the electrodes may be used, for example, to measure an impedance of a tissue bite present between the clamp arm 1 142a, 1 146 and the blade 1 142b, 1 149.
  • the generator 1 100 may provide a signal (e.g., a non-therapeutic signal) to the electrodes.
  • the impedance of the tissue bite may be found, for example, by monitoring the current, voltage, etc. of the signal.
  • the generator 1 100 may comprise several separate functional elements, such as modules and/or blocks, as shown in FIG. 24, a diagram of the surgical system 1000 of FIG. 22.
  • Different functional elements or modules may be configured for driving the different kinds of surgical devices 1 104, 1 106, 1 108.
  • an ultrasonic generator module may drive an ultrasonic device, such as the ultrasonic device 1 104.
  • electrosurgery/RF generator module may drive the electrosurgical device 1 106.
  • the modules may generate respective drive signals for driving the surgical devices 1 104, 1 106, 1 108.
  • the ultrasonic generator module and/or the electrosurgery/RF generator module each may be formed integrally with the generator 1 100.
  • one or more of the modules may be provided as a separate circuit module electrically coupled to the generator 1 100. (The modules are shown in phantom to illustrate this option.)
  • the electrosurgery/RF generator module may be formed integrally with the ultrasonic generator module, or vice versa.
  • the ultrasonic generator module may produce a drive signal or signals of particular voltages, currents, and frequencies (e.g. 55,500 cycles per second, or Hz).
  • the drive signal or signals may be provided to the ultrasonic device 1 104, and specifically to the transducer 1 120, which may operate, for example, as described above.
  • the generator 1 100 may be configured to produce a drive signal of a particular voltage, current, and/or frequency output signal that can be stepped with high resolution, accuracy, and repeatability.
  • the electrosurgery/RF generator module may generate a drive signal or signals with output power sufficient to perform bipolar electrosurgery using radio frequency (RF) energy.
  • the drive signal may be provided, for example, to the electrodes of the electrosurgical device 1 106, for example, as described above.
  • the generator 1 100 may be configured for therapeutic purposes by applying electrical energy to the tissue sufficient for treating the tissue (e.g., coagulation, cauterization, tissue welding, etc.).
  • the generator 1 100 may comprise an input device 2150 (FIG. 27B) located, for example, on a front panel of the generator 1 100 console.
  • the input device 2150 may comprise any suitable device that generates signals suitable for programming the operation of the generator 1 100. In operation, the user can program or otherwise control operation of the generator 1 100 using the input device 2150.
  • the input device 2150 may comprise any suitable device that generates signals that can be used by the generator (e.g., by one or more processors contained in the generator) to control the operation of the generator 1 100 (e.g., operation of the ultrasonic generator module and/or electrosurgery/RF generator module).
  • the input device 2150 includes one or more of: buttons, switches,
  • the input device 2150 may comprise a suitable user interface, such as one or more user interface screens displayed on a touch screen monitor, for example. Accordingly, by way of the input device 2150, the user can set or program various operating parameters of the generator, such as, for example, current (I), voltage (V), frequency (f), and/or period (T) of a drive signal or signals generated by the ultrasonic generator module and/or electrosurgery/RF generator module.
  • I current
  • V voltage
  • f frequency
  • T period
  • the generator 1 100 may also comprise an output device 2140 (FIG. 27B) located, for example, on a front panel of the generator 1 100 console.
  • the output device 2140 includes one or more devices for providing a sensory feedback to a user.
  • Such devices may comprise, for example, visual feedback devices (e.g., an LCD display screen, LED indicators), audio feedback devices (e.g., a speaker, a buzzer) or tactile feedback devices (e.g., haptic actuators).
  • modules and/or blocks of the generator 1 100 may be described by way of example, it can be appreciated that a greater or lesser number of modules and/or blocks may be used and still fall within the scope of the aspects. Further, although various aspects may be described in terms of modules and/or blocks to facilitate description, such modules and/or blocks may be implemented by one or more hardware components, e.g., processors, Digital Signal Processors (DSPs), Programmable Logic Devices (PLDs), Application Specific
  • ASICs Integrated Circuits
  • registers e.g., registers and/or software components, e.g., programs, subroutines, logic and/or combinations of hardware and software components.
  • the ultrasonic generator drive module and electrosurgery/RF drive module 1 1 10 may comprise one or more embedded applications implemented as firmware, software, hardware, or any combination thereof.
  • the modules may comprise various executable modules such as software, programs, data, drivers, application program interfaces (APIs), and so forth.
  • the firmware may be stored in nonvolatile memory (NVM), such as in bit- masked read-only memory (ROM) or flash memory. In various implementations, storing the firmware in ROM may preserve flash memory.
  • the NVM may comprise other types of memory including, for example, programmable ROM (PROM), erasable programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM), or battery backed random-access memory (RAM) such as dynamic RAM (DRAM), Double-Data-Rate DRAM (DDRAM), and/or synchronous DRAM (SDRAM).
  • PROM programmable ROM
  • EPROM erasable programmable ROM
  • EEPROM electrically erasable programmable ROM
  • RAM battery backed random-access memory
  • DRAM dynamic RAM
  • DDRAM Double-Data-Rate DRAM
  • SDRAM synchronous DRAM
  • the modules comprise a hardware component implemented as a processor for executing program instructions for monitoring various measurable characteristics of the devices 1 104, 1 106, 1 108 and generating a corresponding output drive signal or signals for operating the devices 1 104, 1 106, 1 108.
  • the drive signal may drive the ultrasonic transducer 1 120 in cutting and/or coagulation operating modes. Electrical characteristics of the device 1 104 and/or tissue may be measured and used to control operational aspects of the generator 1 100 and/or provided as feedback to the user. In aspects in which the generator 1 100 is used in conjunction with the device 1 106, the drive signal may supply electrical energy (e.g., RF energy) to the end effector 1 124 in cutting, coagulation and/or desiccation modes. Electrical characteristics of the device 1 106 and/or tissue may be measured and used to control operational aspects of the generator 1 100 and/or provided as feedback to the user.
  • electrical energy e.g., RF energy
  • the hardware components may be implemented as DSP, PLD, ASIC, circuits, and/or registers.
  • the processor may be configured to store and execute computer software program instructions to generate the step function output signals for driving various components of the devices 1 104, 1 106, 1 108, such as the ultrasonic transducer 1 120 and the end effectors 1 122, 1 124, 1 125.
  • An electromechanical ultrasonic system includes an ultrasonic transducer, a waveguide, and an ultrasonic blade.
  • the electromechanical ultrasonic system has an initial resonant frequency defined by the physical properties of the ultrasonic transducer, the waveguide, and the ultrasonic blade.
  • the ultrasonic transducer is excited by an alternating voltage V g (t) and current l g (t) signal equal to the resonant frequency of the electromechanical ultrasonic system.
  • V g (t) and current l g (t) signal equal to the resonant frequency of the electromechanical ultrasonic system.
  • the compliance of the ultrasonic blade causes the resonant frequency of the electromechanical ultrasonic system to shift.
  • the inductive impedance is no longer equal to the capacitive impedance causing a mismatch between the drive frequency and the resonant frequency of the electromechanical ultrasonic system.
  • the system is now operating“off-resonance.”
  • the mismatch between the drive frequency and the resonant frequency is manifested as a phase difference between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer.
  • the generator electronics can easily monitor the phase difference between the voltage V g (t) and current l g (t) signals and can continuously adjust the drive frequency until the phase difference is once again zero. At this point, the new drive frequency is equal to the new resonant frequency of the electromechanical ultrasonic system.
  • the change in phase and/or frequency can be used as an indirect measurement of the ultrasonic blade temperature.
  • the electromechanical properties of the ultrasonic transducer may be modeled as an equivalent circuit comprising a first branch having a static capacitance and a second“motional” branch having a serially connected inductance, resistance and capacitance that define the electromechanical properties of a resonator.
  • Known ultrasonic generators may include a tuning inductor for tuning out the static capacitance at a resonant frequency so that substantially all of generator’s drive signal current flows into the motional branch. Accordingly, by using a tuning inductor, the generator’s drive signal current represents the motional branch current, and the generator is thus able to control its drive signal to maintain the ultrasonic transducer’s resonant frequency.
  • the tuning inductor may also transform the phase impedance plot of the ultrasonic transducer to improve the generator’s frequency lock capabilities.
  • the tuning inductor must be matched with the specific static capacitance of an ultrasonic transducer at the operational resonance frequency.
  • a different ultrasonic transducer having a different static capacitance requires a different tuning inductor.
  • FIG. 25 illustrates an equivalent circuit 1500 of an ultrasonic transducer, such as the ultrasonic transducer 1 120, according to one aspect.
  • the circuit 1500 comprises a first “motional” branch having a serially connected inductance L s , resistance R s and capacitance C s that define the electromechanical properties of the resonator, and a second capacitive branch having a static capacitance C 0 .
  • Drive current l g (t) may be received from a generator at a drive voltage V g (t), with motional current l m (t) flowing through the first branch and current l g (t)-l m (t) flowing through the capacitive branch.
  • Control of the electromechanical properties of the ultrasonic transducer may be achieved by suitably controlling l g (t) and V g (t).
  • known generator architectures may include a tuning inductor U (shown in phantom in FIG. 25) in a parallel resonance circuit for tuning out the static capacitance C 0 at a resonant frequency so that substantially all of the generator’s current output l g (t) flows through the motional branch. In this way, control of the motional branch current l m (t) is achieved by controlling the generator current output l g (t).
  • the tuning inductor L t is specific to the static capacitance C 0 of an ultrasonic transducer, however, and a different ultrasonic transducer having a different static capacitance requires a different tuning inductor L t . Moreover, because the tuning inductor U is matched to the nominal value of the static capacitance C 0 at a single resonant frequency, accurate control of the motional branch current l m (t) is assured only at that frequency. As frequency shifts down with transducer temperature, accurate control of the motional branch current is compromised.
  • the generator 1 100 may not rely on a tuning inductor U to monitor the motional branch current l m (t). Instead, the generator 1 100 may use the measured value of the static capacitance C 0 in between applications of power for a specific ultrasonic surgical device 1 104 (along with drive signal voltage and current feedback data) to determine values of the motional branch current l m (t) on a dynamic and ongoing basis (e.g., in real-time).
  • Such aspects of the generator 1 100 are therefore able to provide virtual tuning to simulate a system that is tuned or resonant with any value of static capacitance C 0 at any frequency, and not just at a single resonant frequency dictated by a nominal value of the static capacitance C 0 .
  • FIG. 26 is a simplified block diagram of one aspect of the generator 1 100 for providing inductorless tuning as described above, among other benefits.
  • FIGS. 27A-27C illustrate an architecture of the generator 1 100 of FIG. 26 according to one aspect.
  • the generator 1 100 may comprise a patient isolated stage 1520 in communication with a non-isolated stage 1540 via a power transformer 1560.
  • a secondary winding 1580 of the power transformer 1560 is contained in the isolated stage 1520 and may comprise a tapped configuration (e.g., a center-tapped or non-center tapped configuration) to define drive signal outputs 1600a, 1600b, 1600c for outputting drive signals to different surgical devices, such as, for example, an ultrasonic surgical device 1 104 and an electrosurgical device 1 106.
  • drive signal outputs 1600a, 1600b, 1600c may output a drive signal (e.g., a 420V RMS drive signal) to an ultrasonic surgical device 1 104
  • drive signal outputs 1600a, 1600b, 1600c may output a drive signal (e.g., a 100V RMS drive signal) to an electrosurgical device 1 106, with output 1600b corresponding to the center tap of the power transformer 1560
  • the non-isolated stage 1540 may comprise a power amplifier 1620 having an output connected to a primary winding 1640 of the power transformer 1560.
  • the power amplifier 1620 may comprise a push-pull amplifier, for example.
  • the non-isolated stage 1540 may further comprise a programmable logic device 1660 for supplying a digital output to a digital-to-analog converter (DAC) 1680, which in turn supplies a corresponding analog signal to an input of the power amplifier 1620.
  • the programmable logic device 1660 may comprise a field-programmable gate array (FPGA), for example.
  • FPGA field-programmable gate array
  • the programmable logic device 1660 by virtue of controlling the power amplifier’s 1620 input via the DAC 1680, may therefore control any of a number of parameters (e.g., frequency, waveform shape, waveform amplitude) of drive signals appearing at the drive signal outputs 1600a, 1600b, 1600c.
  • the programmable logic device 1660 in conjunction with a processor (e.g., processor 1740 discussed below), may implement a number of digital signal processing (DSP)- based and/or other control algorithms to control parameters of the drive signals output by the generator 1 100.
  • DSP digital signal processing
  • Power may be supplied to a power rail of the power amplifier 1620 by a switch-mode regulator 1700.
  • the switch-mode regulator 1700 may comprise an adjustable buck regulator, for example.
  • the non-isolated stage 1540 may further comprise a processor 1740, which in one aspect may comprise a DSP processor such as an ADSP-21469 SHARC DSP, available from Analog Devices, Norwood, Mass., for example.
  • the processor 1740 may control operation of the switch-mode power converter 1700 responsive to voltage feedback data received from the power amplifier 1620 by the processor 1740 via an analog-to-digital converter (ADC) 1760.
  • ADC analog-to-digital converter
  • the processor 1740 may receive as input, via the ADC 1760, the waveform envelope of a signal (e.g., an RF signal) being amplified by the power amplifier 1620.
  • the processor 1740 may then control the switch-mode regulator 1700 (e.g., via a pulse-width modulated (PWM) output) such that the rail voltage supplied to the power amplifier 1620 tracks the waveform envelope of the amplified signal.
  • PWM pulse-width modulated
  • the processor 1740 may be configured for wired or wireless communication.
  • the programmable logic device 1660 in conjunction with the processor 1740, may implement a direct digital synthesizer (DDS) control scheme to control the waveform shape, frequency and/or amplitude of drive signals output by the generator 1 100.
  • DDS direct digital synthesizer
  • the programmable logic device 1660 may implement a DDS control algorithm 2680 (FIG. 28A) by recalling waveform samples stored in a dynamically-updated look-up table (LUT), such as a RAM LUT which may be embedded in an FPGA.
  • LUT dynamically-updated look-up table
  • This control algorithm is particularly useful for ultrasonic applications in which an ultrasonic transducer, such as the ultrasonic transducer 1 120, may be driven by a clean sinusoidal current at its resonant frequency. Because other frequencies may excite parasitic resonances, minimizing or reducing the total distortion of the motional branch current may correspondingly minimize or reduce undesirable resonance effects.
  • voltage and current feedback data based on the drive signal may be input into an algorithm, such as an error control algorithm implemented by the processor 1740, which compensates for distortion by suitably pre-distorting or modifying the waveform samples stored in the LUT on a dynamic, ongoing basis (e.g., in real-time).
  • the amount or degree of pre-distortion applied to the LUT samples may be based on the error between a computed motional branch current and a desired current waveform shape, with the error being determined on a sample-by sample basis.
  • the pre-distorted LUT samples when processed through the drive circuit, may result in a motional branch drive signal having the desired waveform shape (e.g., sinusoidal) for optimally driving the ultrasonic transducer.
  • the LUT waveform samples will therefore not represent the desired waveform shape of the drive signal, but rather the waveform shape that is required to ultimately produce the desired waveform shape of the motional branch drive signal when distortion effects are taken into account.
  • the non-isolated stage 1540 may further comprise an ADC 1780 and an ADC 1800 coupled to the output of the power transformer 1560 via respective isolation transformers 1820, 1840 for respectively sampling the voltage and current of drive signals output by the generator 1 100.
  • the ADCs 1780, 1800 may be configured to sample at high speeds (e.g., 80 Msps) to enable oversampling of the drive signals.
  • the sampling speed of the ADCs 1780, 1800 may enable approximately 200X (depending on drive frequency) oversampling of the drive signals.
  • the sampling operations of the ADCs 1780, 1800 may be performed by a single ADC receiving input voltage and current signals via a two-way multiplexer.
  • the use of high-speed sampling in aspects of the generator 1 100 may enable, among other things, calculation of the complex current flowing through the motional branch (which may be used in certain aspects to implement DDS-based waveform shape control described above), accurate digital filtering of the sampled signals, and calculation of real power consumption with a high degree of precision.
  • Voltage and current feedback data output by the ADCs 1780, 1800 may be received and processed (e.g., FIFO buffering, multiplexing) by the programmable logic device 1660 and stored in data memory for subsequent retrieval by, for example, the processor 1740.
  • voltage and current feedback data may be used as input to an algorithm for pre-distorting or modifying LUT waveform samples on a dynamic and ongoing basis.
  • each stored voltage and current feedback data pair may be indexed based on, or otherwise associated with, a corresponding LUT sample that was output by the programmable logic device 1660 when the voltage and current feedback data pair was acquired. Synchronization of the LUT samples and the voltage and current feedback data in this manner contributes to the correct timing and stability of the pre-distortion algorithm.
  • the voltage and current feedback data may be used to control the frequency and/or amplitude (e.g., current amplitude) of the drive signals.
  • voltage and current feedback data may be used to determine impedance phase, e.g., the phase difference between the voltage and current drive signals. The frequency of the drive signal may then be controlled to minimize or reduce the difference between the determined impedance phase and an impedance phase setpoint (e.g., 0°), thereby minimizing or reducing the effects of harmonic distortion and correspondingly enhancing impedance phase
  • phase impedance and a frequency control signal may be implemented in the processor 1740, for example, with the frequency control signal being supplied as input to a DDS control algorithm implemented by the programmable logic device 1660.
  • the impedance phase may be determined through Fourier analysis.
  • the phase difference between the generator voltage V g (t) and generator current l g (t) driving signals may be determined using the Fast Fourier Transform (FFT) or the Discrete Fourier Transform (DFT) as follows:
  • f is the phase angle
  • f is the frequency
  • t is time
  • Another technique for determining the phase difference between the voltage V g (t) and current l g (t) signals is the zero-crossing method and produces highly accurate results.
  • each negative to positive zero crossing of voltage signal V g (t) triggers the start of a pulse
  • each negative to positive zero crossing of current signal l g (t) triggers the end of the pulse.
  • the result is a pulse train with a pulse width proportional to the phase angle between the voltage signal and the current signal.
  • the pulse train may be passed through an averaging filter to yield a measure of the phase difference.
  • the analog voltage V g (t) and current l g (t) signals are converted to digital signals that are high if the analog signal is positive and low if the analog signal is negative. High accuracy phase estimates require sharp transitions between high and low.
  • a Schmitt trigger along with an RC stabilization network may be employed to convert the analog signals into digital signals.
  • an edge triggered RS flip-flop and ancillary circuitry may be employed.
  • the zero-crossing technique may employ an exclusive OR (XOR) gate.
  • phase difference between the voltage and current signals include Lissajous figures and monitoring the image; methods such as the three- voltmeter method, the crossed-coil method, vector voltmeter and vector impedance methods; and using phase standard instruments, phase-locked loops, and other techniques as described in Phase Measurement, Peter O’Shea, 2000 CRC Press LLC, ⁇ http://www.engnetbase.com>, which is incorporated herein by reference.
  • the current feedback data may be monitored in order to maintain the current amplitude of the drive signal at a current amplitude setpoint.
  • the current amplitude setpoint may be specified directly or determined indirectly based on specified voltage amplitude and power setpoints.
  • control of the current amplitude may be implemented by control algorithm, such as, for example, a proportional-integral-derivative (PID) control algorithm, in the processor 1740.
  • PID proportional-integral-derivative
  • Variables controlled by the control algorithm to suitably control the current amplitude of the drive signal may include, for example, the scaling of the LUT waveform samples stored in the programmable logic device 1660 and/or the full-scale output voltage of the DAC 1680 (which supplies the input to the power amplifier 1620) via a DAC 1860.
  • the non-isolated stage 1540 may further comprise a processor 1900 for providing, among other things, user interface (Ul) functionality.
  • the processor 1900 may comprise an Atmel AT91 SAM9263 processor having an ARM 926EJ-S core, available from Atmel Corporation, San Jose, Calif., for example.
  • Ul functionality supported by the processor 1900 may include audible and visual user feedback, communication with peripheral devices (e.g., via a Universal Serial Bus (USB) interface), communication with a foot switch 1430, communication with an input device 2150 (e.g., a touch screen display) and
  • USB Universal Serial Bus
  • the processor 1900 may communicate with the processor 1740 and the programmable logic device (e.g., via a serial peripheral interface (SPI) bus). Although the processor 1900 may primarily support Ul functionality, it may also coordinate with the processor 1740 to implement hazard mitigation in certain aspects. For example, the processor 1900 may be programmed to monitor various aspects of user input and/or other inputs (e.g., touch screen inputs 2150, foot switch 1430 inputs, temperature sensor inputs 2160) and may disable the drive output of the generator 1 100 when an erroneous condition is detected.
  • SPI serial peripheral interface
  • both the processor 1740 (FIG. 26, 27A) and the processor 1900 (FIG. 26, 27B) may determine and monitor the operating state of the generator 1 100.
  • the operating state of the generator 1 100 may dictate, for example, which control and/or diagnostic processes are implemented by the processor 1740.
  • the operating state of the generator 1 100 may dictate, for example, which elements of a user interface (e.g., display screens, sounds) are presented to a user.
  • the 1900 may independently maintain the current operating state of the generator 1 100 and recognize and evaluate possible transitions out of the current operating state.
  • the processor 1740 may function as the master in this relationship and determine when transitions between operating states are to occur.
  • the processor 1900 may be aware of valid transitions between operating states and may confirm if a particular transition is appropriate. For example, when the processor 1740 instructs the processor 1900 to transition to a specific state, the processor 1900 may verify that the requested transition is valid. In the event that a requested transition between states is determined to be invalid by the processor 1900, the processor 1900 may cause the generator 1 100 to enter a failure mode.
  • the non-isolated stage 1540 may further comprise a controller 1960 (FIG. 26, 27B) for monitoring input devices 2150 (e.g., a capacitive touch sensor used for turning the generator 1 100 on and off, a capacitive touch screen).
  • the controller 1960 may comprise at least one processor and/or other controller device in communication with the processor 1900.
  • the controller 1960 may comprise a processor (e.g., a Mega168 8-bit controller available from Atmel) configured to monitor user input provided via one or more capacitive touch sensors.
  • the controller 1960 may comprise a touch screen controller (e.g., a QT5480 touch screen controller available from Atmel) to control and manage the acquisition of touch data from a capacitive touch screen.
  • a touch screen controller e.g., a QT5480 touch screen controller available from Atmel
  • the controller 1960 may continue to receive operating power (e.g., via a line from a power supply of the generator 1 100, such as the power supply 21 10 (FIG. 26) discussed below). In this way, the controller 1960 may continue to monitor an input device 2150 (e.g., a capacitive touch sensor located on a front panel of the generator 1 100) for turning the generator 1 100 on and off.
  • an input device 2150 e.g., a capacitive touch sensor located on a front panel of the generator 1 100
  • the controller 1960 may wake the power supply (e.g., enable operation of one or more DC/DC voltage converters 2130 (FIG. 26) of the power supply 21 10) if activation of the“on/off input device 2150 by a user is detected.
  • the controller 1960 may therefore initiate a sequence for transitioning the generator 1 100 to a“power on” state.
  • the controller 1960 may initiate a sequence for transitioning the generator 1 100 to the“power off’ state if activation of the“on/off” input device 2150 is detected when the generator 1 100 is in the“power on” state.
  • the controller 1960 may report activation of the“on/off” input device 2150 to the processor 1900, which in turn implements the necessary process sequence for transitioning the generator 1 100 to the“power off’ state.
  • the controller 1960 may have no independent ability for causing the removal of power from the generator 1 100 after its“power on” state has been established.
  • the controller 1960 may cause the generator 1 100 to provide audible or other sensory feedback for alerting the user that a“power on” or“power off” sequence has been initiated. Such an alert may be provided at the beginning of a“power on” or “power off” sequence and prior to the commencement of other processes associated with the sequence.
  • the isolated stage 1520 may comprise an instrument interface circuit 1980 to, for example, provide a communication interface between a control circuit of a surgical device (e.g., a control circuit comprising handpiece switches) and components of the non-isolated stage 1540, such as, for example, the programmable logic device 1660, the processor 1740 and/or the processor 1900.
  • the instrument interface circuit 1980 may exchange information with components of the non-isolated stage 1540 via a communication link that maintains a suitable degree of electrical isolation between the stages 1520, 1540, such as, for example, an infrared (IR)-based communication link.
  • Power may be supplied to the instrument interface circuit 1980 using, for example, a low-dropout voltage regulator powered by an isolation transformer driven from the non-isolated stage 1540.
  • the instrument interface circuit 1980 may comprise a programmable logic device 2000 (e.g., an FPGA) in communication with a signal conditioning circuit 2020 (FIG. 26 and FIG. 27C).
  • the signal conditioning circuit 2020 may be configured to receive a periodic signal from the programmable logic device 2000 (e.g., a 2 kHz square wave) to generate a bipolar interrogation signal having an identical frequency.
  • the interrogation signal may be generated, for example, using a bipolar current source fed by a differential amplifier.
  • the interrogation signal may be communicated to a surgical device control circuit (e.g., by using a conductive pair in a cable that connects the generator 1 100 to the surgical device) and monitored to determine a state or configuration of the control circuit.
  • control circuit may comprise a number of switches, resistors and/or diodes to modify one or more characteristics (e.g., amplitude, rectification) of the interrogation signal such that a state or configuration of the control circuit is uniquely discernible based on the one or more characteristics (e.g., amplitude, rectification) of the interrogation signal such that a state or configuration of the control circuit is uniquely discernible based on the one or more characteristics (e.g., amplitude, rectification) of the interrogation signal such that a state or configuration of the control circuit is uniquely discernible based on the one or more
  • the signal conditioning circuit 2020 may comprise an ADC for generating samples of a voltage signal appearing across inputs of the control circuit resulting from passage of interrogation signal therethrough.
  • the programmable logic device 2000 (or a component of the non-isolated stage 1540) may then determine the state or configuration of the control circuit based on the ADC samples.
  • the instrument interface circuit 1980 may comprise a first data circuit interface 2040 to enable information exchange between the programmable logic device 2000 (or other element of the instrument interface circuit 1980) and a first data circuit disposed in or otherwise associated with a surgical device.
  • a first data circuit 2060 may be disposed in a cable integrally attached to a surgical device handpiece, or in an adaptor for interfacing a specific surgical device type or model with the generator 1 100.
  • the first data circuit may comprise a non-volatile storage device, such as an electrically erasable programmable read-only memory (EEPROM) device.
  • EEPROM electrically erasable programmable read-only memory
  • the first data circuit interface 2040 may be implemented separately from the programmable logic device 2000 and comprise suitable circuitry (e.g., discrete logic devices, a processor) to enable communication between the programmable logic device 2000 and the first data circuit. In other aspects, the first data circuit interface 2040 may be integral with the programmable logic device 2000.
  • the first data circuit 2060 may store information pertaining to the particular surgical device with which it is associated. Such information may include, for example, a model number, a serial number, a number of operations in which the surgical device has been used, and/or any other type of information. This information may be read by the instrument interface circuit 1980 (e.g., by the programmable logic device 2000), transferred to a component of the non-isolated stage 1540 (e.g., to programmable logic device 1660, processor 1740 and/or processor 1900) for presentation to a user via an output device 2140 and/or for controlling a function or operation of the generator 1 100.
  • the instrument interface circuit 1980 e.g., by the programmable logic device 2000
  • a component of the non-isolated stage 1540 e.g., to programmable logic device 1660, processor 1740 and/or processor 1900
  • any type of information may be communicated to first data circuit 2060 for storage therein via the first data circuit interface 2040 (e.g., using the programmable logic device 2000).
  • Such information may comprise, for example, an updated number of operations in which the surgical device has been used and/or dates and/or times of its usage.
  • a surgical instrument may be detachable from a handpiece (e.g., instrument 1 106 may be detachable from handpiece 1 107) to promote instrument interchangeability and/or disposability.
  • known generators may be limited in their ability to recognize particular instrument configurations being used and to optimize control and diagnostic processes accordingly.
  • the addition of readable data circuits to surgical device instruments to address this issue is problematic from a compatibility standpoint, however. For example, it may be impractical to design a surgical device to maintain backward compatibility with generators that lack the requisite data reading functionality due to, for example, differing signal schemes, design complexity and cost.
  • Other aspects of instruments address these concerns by using data circuits that may be implemented in existing surgical instruments economically and with minimal design changes to preserve compatibility of the surgical devices with current generator platforms.
  • aspects of the generator 1 100 may enable communication with instrument-based data circuits.
  • the generator 1 100 may be configured to communicate with a second data circuit (e.g., a data circuit) contained in an instrument (e.g., instrument 1 104, 1 106 or 1 108) of a surgical device.
  • the instrument interface circuit 1980 may comprise a second data circuit interface 2100 to enable this communication.
  • the second data circuit interface 2100 may comprise a tri-state digital interface, although other interfaces may also be used.
  • the second data circuit may generally be any circuit for transmitting and/or receiving data.
  • the second data circuit may store information pertaining to the particular surgical instrument with which it is associated.
  • Such information may include, for example, a model number, a serial number, a number of operations in which the surgical instrument has been used, and/or any other type of information. Additionally or alternatively, any type of information may be communicated to the second data circuit for storage therein via the second data circuit interface 2100 (e.g., using the
  • the second data circuit may transmit data acquired by one or more sensors (e.g., an instrument-based temperature sensor).
  • the second data circuit may receive data from the generator 1 100 and provide an indication to a user (e.g., an LED indication or other visible indication) based on the received data.
  • the second data circuit and the second data circuit interface 2100 may be configured such that communication between the programmable logic device 2000 and the second data circuit can be effected without the need to provide additional conductors for this purpose (e.g., dedicated conductors of a cable connecting a handpiece to the generator 1 100).
  • information may be communicated to and from the second data circuit using a one-wire bus communication scheme implemented on existing cabling, such as one of the conductors used transmit interrogation signals from the signal conditioning circuit 2020 to a control circuit in a handpiece. In this way, design changes or modifications to the surgical device that might otherwise be necessary are minimized or reduced.
  • the presence of a second data circuit may be“invisible” to generators that do not have the requisite data reading functionality, thus enabling backward compatibility of the surgical device instrument.
  • the isolated stage 1520 may comprise at least one blocking capacitor 2960-1 (FIG. 27C) connected to the drive signal output 1600b to prevent passage of DC current to a patient.
  • a single blocking capacitor may be required to comply with medical regulations or standards, for example. While failure in single-capacitor designs is relatively uncommon, such failure may nonetheless have negative consequences.
  • a second blocking capacitor 2960-2 may be provided in series with the blocking capacitor 2960-1 , with current leakage from a point between the blocking capacitors 2960-1 , 2960-2 being monitored by, for example, an ADC 2980 for sampling a voltage induced by leakage current.
  • the samples may be received by the programmable logic device 2000, for example. Based on changes in the leakage current (as indicated by the voltage samples in the aspect of FIG. 26), the generator 1 100 may determine when at least one of the blocking capacitors 2960-1 , 2960-2 has failed. Accordingly, the aspect of FIG. 26 may provide a benefit over single-capacitor designs having a single point of failure.
  • the non-isolated stage 1540 may comprise a power supply 21 10 for outputting DC power at a suitable voltage and current.
  • the power supply may comprise, for example, a 400 W power supply for outputting a 48 VDC system voltage.
  • the power supply 21 10 may further comprise one or more DC/DC voltage converters 2130 for receiving the output of the power supply to generate DC outputs at the voltages and currents required by the various components of the generator 1 100.
  • one or more of the DC/DC voltage converters 2130 may receive an input from the controller 1960 when activation of the“on/off input device 2150 by a user is detected by the controller 1960 to enable operation of, or wake, the DC/DC voltage converters 2130.
  • FIGS. 28A-28B illustrate certain functional and structural aspects of one aspect of the generator 1 100.
  • Feedback indicating current and voltage output from the secondary winding 1580 of the power transformer 1560 is received by the ADCs 1780, 1800, respectively.
  • the ADCs 1780, 1800 may be implemented as a 2-channel ADC and may sample the feedback signals at a high speed (e.g., 80 Msps) to enable oversampling (e.g., approximately 200x oversampling) of the drive signals.
  • the current and voltage feedback signals may be suitably conditioned in the analog domain (e.g., amplified, filtered) prior to processing by the ADCs 1780, 1800.
  • the programmable logic device 1660 comprises an FPGA.
  • the multiplexed current and voltage feedback samples may be received by a parallel data acquisition port (PDAP) implemented within block 2144 of the processor 1740.
  • the PDAP may comprise a packing unit for implementing any of a number of methodologies for correlating the multiplexed feedback samples with a memory address.
  • feedback samples corresponding to a particular LUT sample output by the programmable logic device 1660 may be stored at one or more memory addresses that are correlated or indexed with the LUT address of the LUT sample.
  • feedback samples corresponding to a particular LUT sample output by the programmable logic device 1660 may be stored, along with the LUT address of the LUT sample, at a common memory location.
  • the feedback samples may be stored such that the address of the LUT sample from which a particular set of feedback samples originated may be subsequently ascertained. As discussed above, synchronization of the LUT sample addresses and the feedback samples in this way contributes to the correct timing and stability of the pre-distortion algorithm.
  • a direct memory access (DMA) controller implemented at block 2166 of the processor 1740 may store the feedback samples (and any LUT sample address data, where applicable) at a designated memory location 2180 of the processor 1740 (e.g., internal RAM).
  • DMA direct memory access
  • Block 2200 of the processor 1740 may implement a pre-distortion algorithm for pre distorting or modifying the LUT samples stored in the programmable logic device 1660 on a dynamic, ongoing basis.
  • pre-distortion of the LUT samples may compensate for various sources of distortion present in the output drive circuit of the generator 1 100.
  • the pre-distorted LUT samples, when processed through the drive circuit, will therefore result in a drive signal having the desired waveform shape (e.g., sinusoidal) for optimally driving the ultrasonic transducer.
  • the current through the motional branch of the ultrasonic transducer is determined.
  • the motional branch current may be determined using Kirchhoffs Current Law based on, for example, the current and voltage feedback samples stored at memory location 2180 (which, when suitably scaled, may be representative of l g and V g in the model of FIG. 25 discussed above), a value of the ultrasonic transducer static capacitance C 0 (measured or known a priori) and a known value of the drive frequency.
  • a motional branch current sample for each set of stored current and voltage feedback samples associated with a LUT sample may be determined.
  • each motional branch current sample determined at block 2220 is compared to a sample of a desired current waveform shape to determine a difference, or sample amplitude error, between the compared samples.
  • the sample of the desired current waveform shape may be supplied, for example, from a waveform shape LUT 2260 containing amplitude samples for one cycle of a desired current waveform shape.
  • the particular sample of the desired current waveform shape from the LUT 2260 used for the comparison may be dictated by the LUT sample address associated with the motional branch current sample used in the comparison. Accordingly, the input of the motional branch current to block 2240 may be synchronized with the input of its associated LUT sample address to block 2240.
  • the LUT samples stored in the programmable logic device 1660 and the LUT samples stored in the waveform shape LUT 2260 may therefore be equal in number.
  • the desired current waveform shape represented by the LUT samples stored in the waveform shape LUT 2260 may be a fundamental sine wave.
  • Other waveform shapes may be desirable. For example, it is contemplated that a fundamental sine wave for driving main longitudinal motion of an ultrasonic transducer superimposed with one or more other drive signals at other frequencies, such as a third order harmonic for driving at least two mechanical resonances for beneficial vibrations of transverse or other modes, could be used.
  • Each value of the sample amplitude error determined at block 2240 may be transmitted to the LUT of the programmable logic device 1660 (shown at block 2280 in FIG. 28A) along with an indication of its associated LUT address. Based on the value of the sample amplitude error and its associated address (and, optionally, values of sample amplitude error for the same LUT address previously received), the LUT 2280 (or other control block of the programmable logic device 1660) may pre-distort or modify the value of the LUT sample stored at the LUT address such that the sample amplitude error is reduced or minimized.
  • Current and voltage amplitude measurements, power measurements and impedance measurements may be determined at block 2300 of the processor 1740 based on the current and voltage feedback samples stored at memory location 2180.
  • the feedback samples may be suitably scaled and, in certain aspects, processed through a suitable filter 2320 to remove noise resulting from, for example, the data acquisition process and induced harmonic components.
  • the filtered voltage and current samples may therefore substantially represent the fundamental frequency of the generator’s drive output signal.
  • the filter 2320 may be a finite impulse response (FIR) filter applied in the frequency domain.
  • FFT Fast Fourier Transform
  • the resulting frequency spectrum may be used to provide additional generator functionality.
  • the ratio of the second and/or third order harmonic component relative to the fundamental frequency component may be used as a diagnostic indicator.
  • a root mean square (RMS) calculation may be applied to a sample size of the current feedback samples representing an integral number of cycles of the drive signal to generate a measurement l rm s representing the drive signal output current.
  • RMS root mean square
  • a root mean square (RMS) calculation may be applied to a sample size of the voltage feedback samples representing an integral number of cycles of the drive signal to determine a measurement V rm s representing the drive signal output voltage.
  • RMS root mean square
  • the current and voltage feedback samples may be multiplied point by point, and a mean calculation is applied to samples representing an integral number of cycles of the drive signal to determine a measurement P r of the generator’s real output power.
  • measurement P a of the generator’s apparent output power may be determined as the product V rm s lrms.
  • measurement Z m of the load impedance magnitude may be determined as the quotient Vrms/lrms.
  • the quantities l rms , V rms , P r , P a and Z m determined at blocks 2340, 2360, 2380, 2400 and 2420 may be used by the generator 1 100 to implement any of a number of control and/or diagnostic processes. In certain aspects, any of these quantities may be communicated to a user via, for example, an output device 2140 integral with the generator 1 100 or an output device 2140 connected to the generator 1 100 through a suitable
  • Various diagnostic processes may include, without limitation, handpiece integrity, instrument integrity, instrument attachment integrity, instrument overload, approaching instrument overload, frequency lock failure, over-voltage condition, over-current condition, over-power condition, voltage sense failure, current sense failure, audio indication failure, visual indication failure, short circuit condition, power delivery failure, or blocking capacitor failure, for example.
  • Block 2440 of the processor 1740 may implement a phase control algorithm for determining and controlling the impedance phase of an electrical load (e.g., the ultrasonic transducer) driven by the generator 1 100.
  • an electrical load e.g., the ultrasonic transducer
  • Block 2440 of the processor 1740 may implement a phase control algorithm for determining and controlling the impedance phase of an electrical load (e.g., the ultrasonic transducer) driven by the generator 1 100.
  • an impedance phase setpoint e.g., 0°
  • the phase control algorithm receives as input the current and voltage feedback samples stored in the memory location 2180.
  • the feedback samples may be suitably scaled and, in certain aspects, processed through a suitable filter 2460 (which may be identical to filter 2320) to remove noise resulting from the data acquisition process and induced harmonic components, for example.
  • the filtered voltage and current samples may therefore substantially represent the fundamental frequency of the generator’s drive output signal.
  • the current through the motional branch of the ultrasonic transducer is determined. This determination may be identical to that described above in connection with block 2220 of the pre-distortion algorithm.
  • the output of block 2480 may thus be, for each set of stored current and voltage feedback samples associated with a LUT sample, a motional branch current sample.
  • impedance phase is determined based on the synchronized input of motional branch current samples determined at block 2480 and corresponding voltage feedback samples. In certain aspects, the impedance phase is determined as the average of the impedance phase measured at the rising edge of the waveforms and the impedance phase measured at the falling edge of the waveforms. [0343] At block 2520 of the of the phase control algorithm, the value of the impedance phase determined at block 2220 is compared to phase setpoint 2540 to determine a difference, or phase error, between the compared values.
  • a frequency output for controlling the frequency of the drive signal is determined.
  • the value of the frequency output may be continuously adjusted by the block 2560 and transferred to a DDS control block 2680 (discussed below) in order to maintain the impedance phase determined at block 2500 at the phase setpoint (e.g., zero phase error).
  • the impedance phase may be regulated to a 0° phase setpoint. In this way, any harmonic distortion will be centered about the crest of the voltage waveform, enhancing the accuracy of phase impedance determination.
  • Block 2580 of the processor 1740 may implement an algorithm for modulating the current amplitude of the drive signal in order to control the drive signal current, voltage and power in accordance with user specified setpoints, or in accordance with requirements specified by other processes or algorithms implemented by the generator 1 100. Control of these quantities may be realized, for example, by scaling the LUT samples in the LUT 2280 and/or by adjusting the full-scale output voltage of the DAC 1680 (which supplies the input to the power amplifier 1620) via a DAC 1860.
  • Block 2600 (which may be implemented as a PID controller in certain aspects) may receive, as input, current feedback samples (which may be suitably scaled and filtered) from the memory location 2180.
  • the current feedback samples may be compared to a“current demand” l d value dictated by the controlled variable (e.g., current, voltage or power) to determine if the drive signal is supplying the necessary current.
  • the current demand l d may be specified directly by a current setpoint 2620A (l sp ). For example, an RMS value of the current feedback data
  • LUT scaling and/or the full-scale output voltage of the DAC 1680 may be adjusted by the block 2600 such that the drive signal current is increased. Conversely, block 2600 may adjust LUT scaling and/or the full-scale output voltage of the DAC 1680 to decrease the drive signal current when the current feedback data indicates an RMS value greater than the current setpoint l sp .
  • the current demand l may be specified indirectly, for example, based on the current required to maintain a desired voltage setpoint 2620B ( V sp ) given the load impedance magnitude Z m measured at block 2420 (e.g. I d V sp /Z m ).
  • Block 2680 may implement a DDS control algorithm for controlling the drive signal by recalling LUT samples stored in the LUT 2280.
  • the DDS control algorithm may be a numerically-controlled oscillator (NCO) algorithm for generating samples of a waveform at a fixed clock rate using a point (memory location)-skipping technique.
  • the NCO algorithm may implement a phase accumulator, or frequency-to-phase converter, that functions as an address pointer for recalling LUT samples from the LUT 2280.
  • the phase accumulator may be a D step size, modulo N phase accumulator, where D is a positive integer representing a frequency control value, and N is the number of LUT samples in the LUT 2280.
  • the phase accumulator may skip addresses in the LUT 2280, resulting in a waveform output having a higher frequency. Accordingly, the frequency of the waveform generated by the DDS control algorithm may therefore be controlled by suitably varying the frequency control value.
  • the frequency control value may be determined based on the output of the phase control algorithm implemented at block 2440.
  • the output of block 2680 may supply the input of DAC 1680, which in turn supplies a corresponding analog signal to an input of the power amplifier 1620.
  • Block 2700 of the processor 1740 may implement a switch-mode converter control algorithm for dynamically modulating the rail voltage of the power amplifier 1620 based on the waveform envelope of the signal being amplified, thereby improving the efficiency of the power amplifier 1620.
  • characteristics of the waveform envelope may be determined by monitoring one or more signals contained in the power amplifier 1620.
  • characteristics of the waveform envelope may be determined by monitoring the minima of a drain voltage (e.g., a MOSFET drain voltage) that is modulated in accordance with the envelope of the amplified signal.
  • a minima voltage signal may be generated, for example, by a voltage minima detector coupled to the drain voltage.
  • the minima voltage signal may be sampled by ADC 1760, with the output minima voltage samples being received at block 2720 of the switch-mode converter control algorithm. Based on the values of the minima voltage samples, block 2740 may control a PWM signal output by a PWM generator 2760, which, in turn, controls the rail voltage supplied to the power amplifier 1620 by the switch-mode regulator 1700. In certain aspects, as long as the values of the minima voltage samples are less than a minima target 2780 input into block 2720, the rail voltage may be modulated in accordance with the waveform envelope as characterized by the minima voltage samples.
  • block 2740 may cause a low rail voltage to be supplied to the power amplifier 1620, with the full rail voltage being supplied only when the minima voltage samples indicate maximum envelope power levels.
  • block 2740 may cause the rail voltage to be maintained at a minimum value suitable for ensuring proper operation of the power amplifier 1620.
  • FIG. 29 is a schematic diagram of one aspect of an electrical circuit 2900, suitable for driving an ultrasonic transducer, such as ultrasonic transducer 1 120, in accordance with at least one aspect of the present disclosure.
  • the electrical circuit 2900 comprises an analog
  • the analog multiplexer 2980 multiplexes various signals from the upstream channels SCL-A, SDA-A such as ultrasonic, battery, and power control circuit.
  • a current sensor 2982 is coupled in series with the return or ground leg of the power supply circuit to measure the current supplied by the power supply.
  • a field effect transistor (FET) temperature sensor 2984 provides the ambient temperature.
  • a pulse width modulation (PWM) watchdog timer 2988 automatically generates a system reset if the main program neglects to periodically service it. It is provided to automatically reset the electrical circuit 2900 when it hangs or freezes because of a software or hardware fault.
  • the electrical circuit 2900 may be configured as an RF driver circuit for driving the ultrasonic transducer or for driving RF electrodes such as the electrical circuit 3600 shown in FIG. 34, for example. Accordingly, with reference now back to FIG. 29, the electrical circuit 2900 can be used to drive both ultrasonic transducers and RF electrodes interchangeably. If driven simultaneously, filter circuits may be provided in the corresponding first stage circuits 3404 (FIG. 32) to select either the ultrasonic waveform or the RF waveform. Such filtering techniques are described in commonly owned U.S. Pat. Pub. No. US-2017-0086910-A1 , titled TECHNIQUES FOR CIRCUIT TOPOLOGIES FOR COMBINED GENERATOR, which is herein incorporated by reference in its entirety.
  • a drive circuit 2986 provides left and right ultrasonic energy outputs.
  • a digital signal that represents the signal waveform is provided to the SCL-A, SDA-A inputs of the analog multiplexer 2980 from a control circuit, such as the control circuit 3200 (FIG. 30).
  • a digital-to- analog converter 2990 (DAC) converts the digital input to an analog output to drive a PWM circuit 2992 coupled to an oscillator 2994.
  • the PWM circuit 2992 provides a first signal to a first gate drive circuit 2996a coupled to a first transistor output stage 2998a to drive a first Ultrasonic (LEFT) energy output.
  • the PWM circuit 2992 also provides a second signal to a second gate drive circuit 2996b coupled to a second transistor output stage 2998b to drive a second
  • the drive circuit 2986, the first and second drive circuits 2996a, 2996b, and the first and second transistor output stages 2998a, 2998b define a first stage amplifier circuit.
  • the control circuit 3200 (FIG. 30) generates a digital waveform 4300 (FIG. 37) employing circuits such as direct digital synthesis (DDS) circuits 4100, 4200 (FIGS. 35 and 36).
  • the DAC 2990 receives the digital waveform 4300 and converts it into an analog waveform, which is received and amplified by the first stage amplifier circuit.
  • FIG. 30 is a schematic diagram of a control circuit 3200, such as control circuit 3212, in accordance with at least one aspect of the present disclosure.
  • the control circuit 3200 is located within a housing of the battery assembly.
  • the battery assembly is the energy source for a variety of local power supplies 3215.
  • the control circuit comprises a main processor 3214 coupled via an interface master 3218 to various downstream circuits by way of outputs SCL-A and SDA-A, SCL-B and SDA-B, SCL-C and SDA-C, for example.
  • the interface master 3218 is a general purpose serial interface such as an l 2 C serial interface.
  • the main processor 3214 also is configured to drive switches 3224 through general purposes input/output (GPIO) 3220, a display 3226 (e.g., and LCD display), and various indicators 3228 through GPIO 3222.
  • GPIO general purposes input/output
  • a watchdog processor 3216 is provided to control the main processor 3214.
  • a switch 3230 is provided in series with a battery 321 1 to activate the control circuit 3212 upon insertion of the battery assembly into a handle assembly of a surgical instrument.
  • the main processor 3214 is coupled to the electrical circuit 2900 (FIG. 29) by way of output terminals SCL-A, SDA-A.
  • the main processor 3214 comprises a memory for storing tables of digitized drive signals or waveforms that are transmitted to the electrical circuit 2900 for driving the ultrasonic transducer 1 120, for example.
  • the main processor 3214 may generate a digital waveform and transmit it to the electrical circuit 2900 or may store the digital waveform for later transmission to the electrical circuit 2900.
  • the main processor 3214 also may provide RF drive by way of output terminals SCL-B, SDA-B and various sensors (e.g., Hall-effect sensors, magneto-rheological fluid (MRF) sensors, etc.) by way of output terminals SCL-C, SDA-C.
  • the main processor 3214 is configured to sense the presence of ultrasonic drive circuitry and/or RF drive circuitry to enable appropriate software and user interface functionality.
  • the main processor 3214 may be an LM 4F230H5QR, available from Texas Instruments, for example. In at least one example, the Texas Instruments
  • LM4F230H5QR is an ARM Cortex-M4F Processor Core comprising on-chip memory of 256 KB single-cycle flash memory, or other non-volatile memory, up to 40 MHz, a prefetch buffer to improve performance above 40 MHz, a 32 KB single-cycle serial random access memory (SRAM), internal read-only memory (ROM) loaded with StellarisWare® software, 2 KB electrically erasable programmable read-only memory (EEPROM), one or more pulse width modulation (PWM) modules, one or more quadrature encoder inputs (QED analog, one or more 12-bit Analog-to-Digital Converters (ADC) with 12 analog input channels, among other features that are readily available from the product datasheet.
  • SRAM serial random access memory
  • ROM internal read-only memory
  • EEPROM electrically erasable programmable read-only memory
  • PWM pulse width modulation
  • quadrature encoder inputs QED analog, one or more 12-bit Analog-to-Digital Converter
  • FIG. 31 shows a simplified block circuit diagram illustrating another electrical circuit 3300 contained within a modular ultrasonic surgical instrument 3334, in accordance with at least one aspect of the present disclosure.
  • the electrical circuit 3300 includes a processor 3302, a clock 3330, a memory 3326, a power supply 3304 (e.g., a battery), a switch 3306, such as a metal-oxide semiconductor field effect transistor (MOSFET) power switch, a drive circuit 3308 (PLL), a transformer 3310, a signal smoothing circuit 3312 (also referred to as a matching circuit and can be, for example, a tank circuit), a sensing circuit 3314, a transducer 1 120, and a shaft assembly (e.g. shaft assembly 1 126, 1 129) comprising an ultrasonic transmission waveguide that terminates at an ultrasonic blade (e.g. ultrasonic blade 1 128, 1 149) which may be referred to herein simply as the waveguide.
  • a processor 3302 e.g.,
  • One feature of the present disclosure that severs dependency on high voltage (120 VAC) input power is the utilization of low- voltage switching throughout the wave-forming process and the amplification of the driving signal only directly before the transformer stage. For this reason, in one aspect of the present disclosure, power is derived from only a battery, or a group of batteries, small enough to fit either within a handle assembly. State-of-the-art battery technology provides powerful batteries of a few centimeters in height and width and a few millimeters in depth. By combining the features of the present disclosure to provide a self-contained and self-powered ultrasonic device, a reduction in manufacturing cost may be achieved.
  • the output of the power supply 3304 is fed to and powers the processor 3302.
  • the processor 3302 receives and outputs signals and, as will be described below, functions according to custom logic or in accordance with computer programs that are executed by the processor 3302.
  • the electrical circuit 3300 can also include a memory 3326, preferably, random access memory (RAM), that stores computer-readable instructions and data.
  • RAM random access memory
  • the output of the power supply 3304 also is directed to the switch 3306 having a duty cycle controlled by the processor 3302.
  • the processor 3302 By controlling the on-time for the switch 3306, the processor 3302 is able to dictate the total amount of power that is ultimately delivered to the transducer 1 120.
  • the switch 3306 is a MOSFET, although other switches and switching configurations are adaptable as well.
  • the output of the switch 3306 is fed to a drive circuit 3308 that contains, for example, a phase detecting phase-locked loop (PLL) and/or a low- pass filter and/or a voltage-controlled oscillator.
  • the output of the switch 3306 is sampled by the processor 3302 to determine the voltage and current of the output signal (VIN and I IN, respectively). These values are used in a feedback architecture to adjust the pulse width modulation of the switch 3306.
  • the duty cycle of the switch 3306 can vary from about 20% to about 80%, depending on the desired and actual output from the switch 3306.
  • the drive circuit 3308 which receives the signal from the switch 3306, includes an oscillatory circuit that turns the output of the switch 3306 into an electrical signal having an ultrasonic frequency, e.g., 55 kHz (VCO).
  • VCO 55 kHz
  • a smoothed-out version of this ultrasonic waveform is ultimately fed to the ultrasonic transducer 1 120 to produce a resonant sine wave along an ultrasonic transmission waveguide.
  • a transformer 3310 At the output of the drive circuit 3308 is a transformer 3310 that is able to step up the low voltage signal(s) to a higher voltage. It is noted that upstream switching, prior to the transformer 3310, is performed at low (e.g., battery driven) voltages, something that, to date, has not been possible for ultrasonic cutting and cautery devices. This is at least partially due to the fact that the device advantageously uses low on-resistance MOSFET switching devices.
  • the switching stage (pre-transformer) can be characterized as low voltage/high current.
  • the MOSFET(s) are run, for example, at 10 V.
  • a separate 10 VDC power supply can be used to feed the MOSFET gate, which ensures that the MOSFET is fully on and a reasonably low on resistance is achieved.
  • the transformer 3310 steps up the battery voltage to 120 V root-mean-square (RMS). Transformers are known in the art and are, therefore, not explained here in detail.
  • circuit component degradation can negatively impact the circuit performance of the circuit.
  • One factor that directly affects component performance is heat.
  • Known circuits generally monitor switching temperatures (e.g., MOSFET temperatures).
  • MOSFET temperatures are no longer a valid indicator of circuit loads and heat.
  • the sensing circuit 3314 senses the temperature of the transformer 3310. This temperature sensing is advantageous as the transformer 3310 is run at or very close to its maximum temperature during use of the device. Additional temperature will cause the core material, e.g., the ferrite, to break down and permanent damage can occur.
  • the present disclosure can respond to a maximum temperature of the transformer 3310 by, for example, reducing the driving power in the transformer 3310, signaling the user, turning the power off, pulsing the power, or other appropriate responses.
  • the processor 3302 is communicatively coupled to the end effector (e.g. 1 122, 1 125), which is used to place material in physical contact with the ultrasonic blade (e.g. 1 128, 1 149). Sensors are provided that measure, at the end effector, a clamping force value (existing within a known range) and, based upon the received clamping force value, the processor 3302 varies the motional voltage V M .
  • a temperature sensor 3332 can be communicatively coupled to the processor 3302, where the processor 3302 is operable to receive and interpret a signal indicating a current temperature of the blade from the temperature sensor 3336 and to determine a target frequency of blade movement based upon the received temperature.
  • force sensors such as strain gages or pressure sensors may be coupled to the trigger (e.g. 1 143, 1 147) to measure the force applied to the trigger by the user.
  • force sensors such as strain gages or pressure sensors may be coupled to a switch button such that displacement intensity corresponds to the force applied by the user to the switch button.
  • the PLL portion of the drive circuit 3308 which is coupled to the processor 3302, is able to determine a frequency of waveguide movement and communicate that frequency to the processor 3302.
  • the processor 3302 stores this frequency value in the memory 3326 when the device is turned off.
  • the processor 3302 is able to determine an elapsed time after the device is shut off and retrieve the last frequency of waveguide movement if the elapsed time is less than a predetermined value. The device can then start up at the last frequency, which, presumably, is the optimum frequency for the current load.
  • the present disclosure provides a modular battery powered handheld surgical instrument with multistage generator circuits.
  • a surgical instrument that includes a battery assembly, a handle assembly, and a shaft assembly where the battery assembly and the shaft assembly are configured to mechanically and electrically connect to the handle assembly.
  • the battery assembly includes a control circuit configured to generate a digital waveform.
  • the handle assembly includes a first stage circuit configured to receive the digital waveform, convert the digital waveform into an analog waveform, and amplify the analog waveform.
  • the shaft assembly includes a second stage circuit coupled to the first stage circuit to receive, amplify, and apply the analog waveform to a load.
  • the present disclosure provides a surgical instrument, comprising: a battery assembly, comprising a control circuit comprising a battery, a memory coupled to the battery, and a processor coupled to the memory and the battery, wherein the processor is configured to generate a digital waveform; a handle assembly comprising a first stage circuit coupled to the processor, the first stage circuit comprising a digital-to-analog (DAC) converter and a first stage amplifier circuit, wherein the DAC is configured to receive the digital waveform and convert the digital waveform into an analog waveform, wherein the first stage amplifier circuit is configured to receive and amplify the analog waveform; and a shaft assembly comprising a second stage circuit coupled to the first stage amplifier circuit to receive the analog waveform, amplify the analog waveform, and apply the analog waveform to a load; wherein the battery assembly and the shaft assembly are configured to mechanically and electrically connect to the handle assembly.
  • DAC digital-to-analog
  • the load may comprise any one of an ultrasonic transducer, an electrode, or a sensor, or any combinations thereof.
  • the first stage circuit may comprise a first stage ultrasonic drive circuit and a first stage high-frequency current drive circuit.
  • the control circuit may be configured to drive the first stage ultrasonic drive circuit and the first stage high-frequency current drive circuit independently or simultaneously.
  • the first stage ultrasonic drive circuit may be configured to couple to a second stage ultrasonic drive circuit.
  • the second stage ultrasonic drive circuit may be configured to couple to an ultrasonic transducer.
  • the first stage high- frequency current drive circuit may be configured to couple to a second stage high-frequency drive circuit.
  • the second stage high-frequency drive circuit may be configured to couple to an electrode.
  • the first stage circuit may comprise a first stage sensor drive circuit.
  • the first stage sensor drive circuit may be configured to a second stage sensor drive circuit.
  • the second stage sensor drive circuit may be configured to couple to a sensor.
  • the present disclosure provides a surgical instrument, comprising: a battery assembly, comprising a control circuit comprising a battery, a memory coupled to the battery, and a processor coupled to the memory and the battery, wherein the processor is configured to generate a digital waveform; a handle assembly comprising a common first stage circuit coupled to the processor, the common first stage circuit comprising a digital-to-analog (DAC) converter and a common first stage amplifier circuit, wherein the DAC is configured to receive the digital waveform and convert the digital waveform into an analog waveform, wherein the common first stage amplifier circuit is configured to receive and amplify the analog waveform; and a shaft assembly comprising a second stage circuit coupled to the common first stage amplifier circuit to receive the analog waveform, amplify the analog waveform, and apply the analog waveform to a load; wherein the battery assembly and the shaft assembly are configured to mechanically and electrically connect to the handle assembly.
  • DAC digital-to-analog
  • the load may comprise any one of an ultrasonic transducer, an electrode, or a sensor, or any combinations thereof.
  • the common first stage circuit may be configured to drive ultrasonic, high-frequency current, or sensor circuits.
  • the common first stage drive circuit may be configured to couple to a second stage ultrasonic drive circuit, a second stage high- frequency drive circuit, or a second stage sensor drive circuit.
  • the second stage ultrasonic drive circuit may be configured to couple to an ultrasonic transducer, the second stage high- frequency drive circuit is configured to couple to an electrode, and the second stage sensor drive circuit is configured to couple to a sensor.
  • the present disclosure provides a surgical instrument, comprising a control circuit comprising a memory coupled to a processor, wherein the processor is configured to generate a digital waveform; a handle assembly comprising a common first stage circuit coupled to the processor, the common first stage circuit configured to receive the digital waveform, convert the digital waveform into an analog waveform, and amplify the analog waveform; and a shaft assembly comprising a second stage circuit coupled to the common first stage circuit to receive and amplify the analog waveform; wherein the shaft assembly is configured to mechanically and electrically connect to the handle assembly.
  • the common first stage circuit may be configured to drive ultrasonic, high-frequency current, or sensor circuits.
  • the common first stage drive circuit may be configured to couple to a second stage ultrasonic drive circuit, a second stage high-frequency drive circuit, or a second stage sensor drive circuit.
  • the second stage ultrasonic drive circuit may be configured to couple to an ultrasonic transducer, the second stage high-frequency drive circuit is configured to couple to an electrode, and the second stage sensor drive circuit is configured to couple to a sensor.
  • FIG. 32 illustrates a generator circuit 3400 partitioned into a first stage circuit 3404 and a second stage circuit 3406, in accordance with at least one aspect of the present disclosure.
  • the surgical instruments of surgical system 1000 described herein may comprise a generator circuit 3400 partitioned into multiple stages.
  • surgical instruments of surgical system 1000 may comprise the generator circuit 3400 partitioned into at least two circuits: the first stage circuit 3404 and the second stage circuit 3406 of amplification enabling operation of RF energy only, ultrasonic energy only, and/or a combination of RF energy and ultrasonic energy.
  • a combination modular shaft assembly 3414 may be powered by the common first stage circuit 3404 located within a handle assembly 3412 and the modular second stage circuit 3406 integral to the modular shaft assembly 3414.
  • a battery assembly 3410 and the shaft assembly 3414 are configured to mechanically and electrically connect to the handle assembly 3412.
  • the end effector assembly is configured to mechanically and electrically connect the shaft assembly 3414.
  • a control stage circuit 3402 may be located in the battery assembly 3410 of the surgical instrument.
  • the control stage circuit 3402 is a control circuit 3200 as described in connection with FIG. 30.
  • the control circuit 3200 comprises a processor 3214, which includes internal memory 3217 (FIG. 32) (e.g., volatile and non-volatile memory), and is electrically coupled to a battery 321 1 .
  • the battery 321 1 supplies power to the first stage circuit 3404, the second stage circuit 3406, and a third stage circuit 3408, respectively.
  • the control circuit 3200 generates a digital waveform 4300 (FIG. 37) using circuits and techniques described in connection with FIGS. 35 and 36.
  • the digital waveform 4300 may be configured to drive an ultrasonic transducer, high-frequency (e.g., RF) electrodes, or a combination thereof either independently or simultaneously. If driven simultaneously, filter circuits may be provided in the corresponding first stage circuits 3404 to select either the ultrasonic waveform or the RF waveform. Such filtering techniques are described in commonly owned U.S. Pat. Pub. No.
  • the first stage circuits 3404 e.g., the first stage ultrasonic drive circuit 3420, the first stage RF drive circuit 3422, and the first stage sensor drive circuit 3424
  • the control circuit 3200 provides the ultrasonic drive signal to the first stage ultrasonic drive circuit 3420 via outputs SCL-A, SDA-A of the control circuit 3200.
  • the first stage ultrasonic drive circuit 3420 is described in detail in connection with FIG. 29.
  • the control circuit 3200 provides the RF drive signal to the first stage RF drive circuit 3422 via outputs SCL-B, SDA-B of the control circuit 3200.
  • the first stage RF drive circuit 3422 is described in detail in connection with FIG. 34.
  • the control circuit 3200 provides the sensor drive signal to the first stage sensor drive circuit 3424 via outputs SCL-C, SDA-C of the control circuit 3200.
  • each of the first stage circuits 3404 includes a digital-to-analog (DAC) converter and a first stage amplifier section to drive the second stage circuits 3406.
  • the outputs of the first stage circuits 3404 are provided to the inputs of the second stage circuits 3406.
  • the control circuit 3200 is configured to detect which modules are plugged into the control circuit 3200.
  • the control circuit 3200 is configured to detect whether the first stage ultrasonic drive circuit 3420, the first stage RF drive circuit 3422, or the first stage sensor drive circuit 3424 located in the handle assembly 3412 is connected to the battery assembly 3410.
  • each of the first stage circuits 3404 can detect which second stage circuits 3406 are connected thereto and that information is provided back to the control circuit 3200 to determine the type of signal waveform to generate.
  • each of the second stage circuits 3406 can detect which third stage circuits 3408 or components are connected thereto and that information is provided back to the control circuit 3200 to determine the type of signal waveform to generate.
  • the second stage circuits 3406 are located in the shaft assembly 3414 of the surgical instrument.
  • the first stage ultrasonic drive circuit 3420 provides a signal to the second stage ultrasonic drive circuit 3430 via outputs US-Left/US-Right.
  • the second stage ultrasonic drive circuit 3430 can include, for example, a transformer, filter, amplifier, and/or signal conditioning circuits.
  • the first stage high- frequency (RF) current drive circuit 3422 provides a signal to the second stage RF drive circuit 3432 via outputs RF-Left/RF-Right.
  • the second stage RF drive circuit 3432 also may include filter, amplifier, and signal conditioning circuits.
  • the first stage sensor drive circuit 3424 provides a signal to the second stage sensor drive circuit 3434 via outputs Sensor-1/Sensor-2.
  • the second stage sensor drive circuit 3434 may include filter, amplifier, and signal conditioning circuits depending on the type of sensor.
  • the outputs of the second stage circuits 3406 are provided to the inputs of the third stage circuits 3408.
  • the third stage circuits 3408 may be located in various assemblies 3416 of the surgical instruments.
  • the second stage ultrasonic drive circuit 3430 provides a drive signal to the ultrasonic transducer 1 120 piezoelectric stack.
  • the ultrasonic transducer 1 120 is located in the ultrasonic transducer assembly of the surgical instrument. In other aspects, however, the ultrasonic transducer 1 120 may be located in the handle assembly 3412, the shaft assembly 3414, or the end effector.
  • the second stage RF drive circuit 3432 provides a drive signal to the RF electrodes 3074a, 3074b, which are generally located in the end effector portion of the surgical instrument.
  • the second stage sensor drive circuit 3434 provides a drive signal to various sensors 3440 located throughout the surgical instrument.
  • FIG. 33 illustrates a generator circuit 3500 partitioned into multiple stages where a first stage circuit 3504 is common to the second stage circuit 3506, in accordance with at least one aspect of the present disclosure.
  • the surgical instruments of surgical system 1000 described herein may comprise generator circuit 3500 partitioned into multiple stages.
  • the surgical instruments of surgical system 1000 may comprise the generator circuit 3500 partitioned into at least two circuits: the first stage circuit 3504 and the second stage circuit 3506 of amplification enabling operation of high-frequency (RF) energy only, ultrasonic energy only, and/or a combination of RF energy and ultrasonic energy.
  • RF high-frequency
  • a combination modular shaft assembly 3514 may be powered by a common first stage circuit 3504 located within the handle assembly 3512 and a modular second stage circuit 3506 integral to the modular shaft assembly 3514.
  • a battery assembly 3510 and the shaft assembly 3514 are configured to mechanically and electrically connect to the handle assembly 3512.
  • the end effector assembly is configured to mechanically and electrically connect the shaft assembly 3514.
  • the battery assembly 3510 portion of the surgical instrument comprises a first control circuit 3502, which includes the control circuit 3200 previously described.
  • the handle assembly 3512 which connects to the battery assembly 3510, comprises a common first stage drive circuit 3420.
  • the first stage drive circuit 3420 is configured to drive ultrasonic, high-frequency (RF) current, and sensor loads.
  • the output of the common first stage drive circuit 3420 can drive any one of the second stage circuits 3506 such as the second stage ultrasonic drive circuit 3430, the second stage high- frequency (RF) current drive circuit 3432, and/or the second stage sensor drive circuit 3434.
  • the common first stage drive circuit 3420 detects which second stage circuit 3506 is located in the shaft assembly 3514 when the shaft assembly 3514 is connected to the handle assembly 3512. Upon the shaft assembly 3514 being connected to the handle assembly 3512, the common first stage drive circuit 3420 determines which one of the second stage circuits 3506 (e.g., the second stage ultrasonic drive circuit 3430, the second stage RF drive circuit 3432, and/or the second stage sensor drive circuit 3434) is located in the shaft assembly 3514. The information is provided to the control circuit 3200 located in the handle assembly 3512 in order to supply a suitable digital waveform 4300 (FIG. 37) to the second stage circuit 3506 to drive the appropriate load, e.g., ultrasonic, RF, or sensor.
  • a suitable digital waveform 4300 FIG. 37
  • identification circuits may be included in various assemblies 3516 in third stage circuit 3508 such as the ultrasonic transducer 1 120, the electrodes 3074a, 3074b, or the sensors 3440.
  • third stage circuit 3508 when a third stage circuit 3508 is connected to a second stage circuit 3506, the second stage circuit 3506 knows the type of load that is required based on the identification information.
  • FIG. 34 is a schematic diagram of one aspect of an electrical circuit 3600 configured to drive a high-frequency current (RF), in accordance with at least one aspect of the present disclosure.
  • the electrical circuit 3600 comprises an analog multiplexer 3680.
  • the analog multiplexer 3680 multiplexes various signals from the upstream channels SCL-A, SDA-A such as RF, battery, and power control circuit.
  • a current sensor 3682 is coupled in series with the return or ground leg of the power supply circuit to measure the current supplied by the power supply.
  • FET field effect transistor
  • a pulse width modulation (PWM) watchdog timer 3688 automatically generates a system reset if the main program neglects to periodically service it. It is provided to
  • the electrical circuit 3600 may be configured for driving RF electrodes or for driving the ultrasonic transducer 1 120 as described in connection with FIG. 29, for example. Accordingly, with reference now back to FIG. 34, the electrical circuit 3600 can be used to drive both ultrasonic and RF electrodes interchangeably.
  • a drive circuit 3686 provides Left and Right RF energy outputs.
  • a digital signal that represents the signal waveform is provided to the SCL-A, SDA-A inputs of the analog multiplexer 3680 from a control circuit, such as the control circuit 3200 (FIG. 30).
  • a digital-to- analog converter 3690 (DAC) converts the digital input to an analog output to drive a PWM circuit 3692 coupled to an oscillator 3694.
  • the PWM circuit 3692 provides a first signal to a first gate drive circuit 3696a coupled to a first transistor output stage 3698a to drive a first RF+ (Left) energy output.
  • the PWM circuit 3692 also provides a second signal to a second gate drive circuit 3696b coupled to a second transistor output stage 3698b to drive a second RF- (Right) energy output.
  • a voltage sensor 3699 is coupled between the RF Left/RF output terminals to measure the output voltage.
  • the drive circuit 3686, the first and second drive circuits 3696a, 3696b, and the first and second transistor output stages 3698a, 3698b define a first stage amplifier circuit.
  • the control circuit 3200 (FIG. 30) generates a digital waveform 4300 (FIG. 37) employing circuits such as direct digital synthesis (DDS) circuits 4100, 4200 (FIGS. 35 and 36).
  • the DAC 3690 receives the digital waveform 4300 and converts it into an analog waveform, which is received and amplified by the first stage amplifier circuit.
  • the ultrasonic or high-frequency current generators of the surgical system 1000 may be configured to generate the electrical signal waveform digitally such that the desired using a predetermined number of phase points stored in a lookup table to digitize the wave shape.
  • the phase points may be stored in a table defined in a memory, a field
  • FIG. 35 illustrates one aspect of a fundamental architecture for a digital synthesis circuit such as a direct digital synthesis (DDS) circuit 4100 configured to generate a plurality of wave shapes for the electrical signal waveform.
  • the generator software and digital controls may command the FPGA to scan the addresses in the lookup table 4104 which in turn provides varying digital input values to a DAC circuit 4108 that feeds a power amplifier.
  • the addresses may be scanned according to a frequency of interest.
  • lookup table 4104 Using such a lookup table 4104 enables generating various types of wave shapes that can be fed into tissue or into a transducer, an RF electrode, multiple transducers simultaneously, multiple RF electrodes simultaneously, or a combination of RF and ultrasonic instruments. Furthermore, multiple lookup tables 4104 that represent multiple wave shapes can be created, stored, and applied to tissue from a generator.
  • the waveform signal may be configured to control at least one of an output current, an output voltage, or an output power of an ultrasonic transducer and/or an RF electrode, or multiples thereof (e.g. two or more ultrasonic transducers and/or two or more RF electrodes).
  • the waveform signal may be configured to drive at least two vibration modes of an ultrasonic transducer of the at least one surgical instrument.
  • a generator may be configured to provide a waveform signal to at least one surgical instrument wherein the waveform signal corresponds to at least one wave shape of a plurality of wave shapes in a table.
  • the waveform signal provided to the two surgical instruments may comprise two or more wave shapes.
  • the table may comprise information associated with a plurality of wave shapes and the table may be stored within the generator.
  • the table may be a direct digital synthesis table, which may be stored in an FPGA of the generator.
  • the table may be addressed by anyway that is convenient for categorizing wave shapes.
  • the table which may be a direct digital synthesis table, is addressed according to a frequency of the waveform signal.
  • the information associated with the plurality of wave shapes may be stored as digital information in the table.
  • the analog electrical signal waveform may be configured to control at least one of an output current, an output voltage, or an output power of an ultrasonic transducer and/or an RF electrode, or multiples thereof (e.g., two or more ultrasonic transducers and/or two or more RF electrodes).
  • the analog electrical signal waveform may be configured to drive at least two vibration modes of an ultrasonic transducer of the at least one surgical instrument.
  • the generator circuit may be configured to provide an analog electrical signal waveform to at least one surgical instrument wherein the analog electrical signal waveform corresponds to at least one wave shape of a plurality of wave shapes stored in a lookup table 4104.
  • the analog electrical signal waveform provided to the two surgical instruments may comprise two or more wave shapes.
  • the lookup table 4104 may comprise information associated with a plurality of wave shapes and the lookup table 4104 may be stored either within the generator circuit or the surgical instrument.
  • the lookup table 4104 may be a direct digital synthesis table, which may be stored in an FPGA of the generator circuit or the surgical instrument.
  • the lookup table 4104 may be addressed by anyway that is convenient for categorizing wave shapes.
  • the lookup table 4104 which may be a direct digital synthesis table, is addressed according to a frequency of the desired analog electrical signal waveform.
  • the information associated with the plurality of wave shapes may be stored as digital information in the lookup table 4104.
  • a digitally-controlled method of generating multiple frequencies from a reference frequency source has evolved and is referred to as direct digital synthesis.
  • the basic architecture is shown in FIG. 35.
  • a DDS circuit is coupled to a processor, controller, or a logic device of the generator circuit and to a memory circuit located in the generator circuit of the surgical system 1000.
  • the DDS circuit 4100 comprises an address counter 4102, lookup table 4104, a register 4106, a DAC circuit 4108, and a filter 41 12.
  • a stable clock f c is received by the address counter 4102 and the register 4106 drives a programmable- read-only-memory (PROM) which stores one or more integral number of cycles of a sinewave (or other arbitrary waveform) in a lookup table 4104.
  • PROM programmable- read-only-memory
  • values stored in the lookup table 4104 are written to the register 4106, which is coupled to the DAC circuit 4108.
  • the corresponding digital amplitude of the signal at the memory location of the lookup table 4104 drives the DAC circuit 4108, which in turn generates an analog output signal 41 10.
  • the spectral purity of the analog output signal 41 10 is determined primarily by the DAC circuit 4108.
  • the phase noise is basically that of the reference clock f c .
  • the first analog output signal 41 10 output from the DAC circuit 4108 is filtered by the filter 41 12 and a second analog output signal 41 14 output by the filter 41 12 is provided to an amplifier having an output coupled to the output of the generator circuit.
  • the second analog output signal has a frequency
  • the DDS circuit 4100 is a sampled data system, issues involved in sampling must be considered: quantization noise, aliasing, filtering, etc.
  • quantization noise For instance, the higher order harmonics of the DAC circuit 4108 output frequencies fold back into the Nyquist bandwidth, making them unfilterable, whereas, the higher order harmonics of the output of phase-locked- loop (PLL) based synthesizers can be filtered.
  • the lookup table 4104 contains signal data for an integral number of cycles. The final output frequency f out can be changed changing the reference clock frequency f c or by reprogramming the PROM.
  • the DDS circuit 4100 may comprise multiple lookup tables 4104 where the lookup table 4104 stores a waveform represented by a predetermined number of samples, wherein the samples define a predetermined shape of the waveform.
  • the lookup table 4104 stores a waveform represented by a predetermined number of samples, wherein the samples define a predetermined shape of the waveform.
  • multiple waveforms having a unique shape can be stored in multiple lookup tables 4104 to provide different tissue treatments based on instrument settings or tissue feedback. Examples of waveforms include high crest factor RF electrical signal waveforms for surface tissue coagulation, low crest factor RF electrical signal waveform for deeper tissue penetration, and electrical signal waveforms that promote efficient touch-up coagulation.
  • the DDS circuit 4100 can create multiple wave shape lookup tables 4104 and during a tissue treatment procedure (e.g.,“on-the-fly” or in virtual real time based on user or sensor inputs) switch between different wave shapes stored in separate lookup tables 4104 based on the tissue effect desired and/or tissue feedback.
  • a tissue treatment procedure e.g.,“on-the-fly” or in virtual real time based on user or sensor inputs
  • the lookup tables 4104 can store electrical signal waveforms shaped to maximize the power delivered into the tissue per cycle (i.e. , trapezoidal or square wave). In other aspects, the lookup tables 4104 can store wave shapes synchronized in such way that they make maximizing power delivery by the multifunction surgical instrument of surgical system 1000 while delivering RF and ultrasonic drive signals. In yet other aspects, the lookup tables 4104 can store electrical signal waveforms to drive ultrasonic and RF therapeutic, and/or sub-therapeutic, energy simultaneously while maintaining ultrasonic frequency lock.
  • Custom wave shapes specific to different instruments and their tissue effects can be stored in the non-volatile memory of the generator circuit or in the non-volatile memory (e.g., EEPROM) of the surgical system 1000 and be fetched upon connecting the multifunction surgical instrument to the generator circuit.
  • EEPROM non-volatile memory
  • An example of an exponentially damped sinusoid, as used in many high crest factor“coagulation” waveforms is shown in FIG. 37.
  • a more flexible and efficient implementation of the DDS circuit 4100 employs a digital circuit called a Numerically Controlled Oscillator (NCO).
  • NCO Numerically Controlled Oscillator
  • FIG. 36 A block diagram of a more flexible and efficient digital synthesis circuit such as a DDS circuit 4200 is shown in FIG. 36.
  • a DDS circuit 4200 is coupled to a processor, controller, or a logic device of the generator and to a memory circuit located either in the generator or in any of the surgical instruments of surgical system 1000.
  • the DDS circuit 4200 comprises a load register 4202, a parallel delta phase register 4204, an adder circuit 4216, a phase register 4208, a lookup table 4210 (phase-to-amplitude converter), a DAC circuit 4212, and a filter 4214.
  • the adder circuit 4216 and the phase register 4208 form part of a phase accumulator 4206.
  • a clock frequency f c is applied to the phase register 4208 and a DAC circuit 4212.
  • the load register 4202 receives a tuning word that specifies output frequency as a fraction of the reference clock frequency signal f c .
  • the output of the load register 4202 is provided to the parallel delta phase register 4204 with a tuning word M.
  • the DDS circuit 4200 includes a sample clock that generates the clock frequency f c , the phase accumulator 4206, and the lookup table 4210 (e.g., phase to amplitude converter).
  • the content of the phase accumulator 4206 is updated once per clock cycle f c .
  • the digital number, M, stored in the parallel delta phase register 4204 is added to the number in the phase register 4208 by the adder circuit 4216. Assuming that the number in the parallel delta phase register 4204 is 00...01 and that the initial contents of the phase accumulator 4206 is 00...00.
  • the phase accumulator 4206 is updated by 00...01 per clock cycle. If the phase accumulator 4206 is 32-bits wide, 232 clock cycles (over 4 billion) are required before the phase accumulator 4206 returns to 00...00, and the cycle repeats.
  • a truncated output 4218 of the phase accumulator 4206 is provided to a phase-to amplitude converter lookup table 4210 and the output of the lookup table 4210 is coupled to a DAC circuit 4212.
  • the truncated output 4218 of the phase accumulator 4206 serves as the address to a sine (or cosine) lookup table.
  • An address in the lookup table corresponds to a phase point on the sinewave from 0° to 360°.
  • the lookup table 4210 contains the corresponding digital amplitude information for one complete cycle of a sinewave.
  • the lookup table 4210 therefore maps the phase information from the phase accumulator 4206 into a digital amplitude word, which in turn drives the DAC circuit 4212.
  • the output of the DAC circuit is a first analog signal 4220 and is filtered by a filter 4214.
  • the output of the filter 4214 is a second analog signal 4222, which is provided to a power amplifier coupled to the output of the generator circuit.
  • the electrical signal waveform may be digitized into 1024 (210) phase points, although the wave shape may be digitized is any suitable number of 2n phase points ranging from 256 (28) to 281 ,474,976,710,656 (248), where n is a positive integer, as shown in TABLE 1 .
  • the electrical signal waveform may be expressed as A n (0 n ), where a normalized amplitude A n at a point n is represented by a phase angle 0 n is referred to as a phase point at point n.
  • the number of discrete phase points n determines the tuning resolution of the DDS circuit 4200 (as well as the DDS circuit 4100 shown in FIG. 35).
  • TABLE 1 specifies the electrical signal waveform digitized into a number of phase points.
  • the generator circuit algorithms and digital control circuits scan the addresses in the lookup table 4210, which in turn provides varying digital input values to the DAC circuit 4212 that feeds the filter 4214 and the power amplifier.
  • the addresses may be scanned according to a frequency of interest.
  • Using the lookup table enables generating various types of shapes that can be converted into an analog output signal by the DAC circuit 4212, filtered by the filter 4214, amplified by the power amplifier coupled to the output of the generator circuit, and fed to the tissue in the form of RF energy or fed to an ultrasonic transducer and applied to the tissue in the form of ultrasonic vibrations which deliver energy to the tissue in the form of heat.
  • the output of the amplifier can be applied to an RF electrode, multiple RF electrodes simultaneously, an ultrasonic transducer, multiple ultrasonic transducers simultaneously, or a combination of RF and ultrasonic transducers, for example.
  • multiple wave shape tables can be created, stored, and applied to tissue from a generator circuit.
  • phase accumulator 4206 steps through 232 possible outputs before it overflows and restarts.
  • phase accumulator 4206 configured to accumulate n-bits (n generally ranges from 24 to 32 in most DDS systems, but as previously discussed n may be selected from a wide range of options), there are 2 n possible phase points.
  • the digital word in the delta phase register, M represents the amount the phase accumulator is incremented per clock cycle. If f c is the clock frequency, then the frequency of the output sinewave is equal to:
  • the electrical signal waveform may be characterized by a current, voltage, or power at a predetermined frequency. Further, where any one of the surgical instruments of surgical system 1000 comprises ultrasonic components, the electrical signal waveform may be configured to drive at least two vibration modes of an ultrasonic transducer of the at least one surgical instrument. Accordingly, the generator circuit may be configured to provide an electrical signal waveform to at least one surgical instrument wherein the electrical signal waveform is characterized by a predetermined wave shape stored in the lookup table 4210 (or lookup table 4104, FIG. 35). Further, the electrical signal waveform may be a combination of two or more wave shapes.
  • the lookup table 4210 may comprise information associated with a plurality of wave shapes.
  • the lookup table 4210 may be generated by the DDS circuit 4200 and may be referred to as a direct digital synthesis table.
  • DDS works by first storing a large repetitive waveform in onboard memory. A cycle of a waveform (sine, triangle, square, arbitrary) can be represented by a predetermined number of phase points as shown in TABLE 1 and stored into memory. Once the waveform is stored into memory, it can be generated at very precise frequencies.
  • the direct digital synthesis table may be stored in a non-volatile memory of the generator circuit and/or may be implemented with a FPGA circuit in the generator circuit.
  • the lookup table 4210 may be addressed by any suitable technique that is convenient for categorizing wave shapes. According to one aspect, the lookup table 4210 is addressed according to a frequency of the electrical signal waveform. Additionally, the information associated with the plurality of wave shapes may be stored as digital information in a memory or as part of the lookup table 4210.
  • the generator circuit may be configured to provide electrical signal waveforms to at least two surgical instruments simultaneously.
  • the generator circuit also may be configured to provide the electrical signal waveform, which may be characterized two or more wave shapes, via an output channel of the generator circuit to the two surgical instruments simultaneously.
  • the electrical signal waveform comprises a first electrical signal to drive an ultrasonic transducer (e.g., ultrasonic drive signal), a second RF drive signal, and/or a combination thereof.
  • an electrical signal waveform may comprise a plurality of ultrasonic drive signals, a plurality of RF drive signals, and/or a combination of a plurality of ultrasonic and RF drive signals.
  • a method of operating the generator circuit comprises generating an electrical signal waveform and providing the generated electrical signal waveform to any one of the surgical instruments of surgical system 1000, where generating the electrical signal waveform comprises receiving information associated with the electrical signal waveform from a memory.
  • the generated electrical signal waveform comprises at least one wave shape.
  • providing the generated electrical signal waveform to the at least one surgical instrument comprises providing the electrical signal waveform to at least two surgical instruments simultaneously.
  • the generator circuit as described herein may allow for the generation of various types of direct digital synthesis tables.
  • wave shapes for RF/Electrosurgery signals suitable for treating a variety of tissue generated by the generator circuit include RF signals with a high crest factor (which may be used for surface coagulation in RF mode), a low crest factor RF signals (which may be used for deeper tissue penetration), and waveforms that promote efficient touch-up coagulation.
  • the generator circuit also may generate multiple wave shapes employing a direct digital synthesis lookup table 4210 and, on the fly, can switch between particular wave shapes based on the desired tissue effect. Switching may be based on tissue impedance and/or other factors.
  • the generator circuit may be configured to generate wave shape(s) that maximize the power into tissue per cycle (i.e. , trapezoidal or square wave).
  • the generator circuit may provide wave shape(s) that are synchronized to maximize the power delivered to the load when driving RF and ultrasonic signals simultaneously and to maintain ultrasonic frequency lock, provided that the generator circuit includes a circuit topology that enables simultaneously driving RF and ultrasonic signals.
  • custom wave shapes specific to instruments and their tissue effects can be stored in a non-volatile memory (NVM) or an instrument EEPROM and can be fetched upon connecting any one of the surgical instruments of surgical system 1000 to the generator circuit.
  • NVM non-volatile memory
  • EEPROM instrument EEPROM
  • the DDS circuit 4200 may comprise multiple lookup tables 4104 where the lookup table 4210 stores a waveform represented by a predetermined number of phase points (also may be referred to as samples), wherein the phase points define a predetermined shape of the waveform.
  • the lookup table 4210 stores a waveform represented by a predetermined number of phase points (also may be referred to as samples), wherein the phase points define a predetermined shape of the waveform.
  • multiple waveforms having a unique shape can be stored in multiple lookup tables 4210 to provide different tissue treatments based on instrument settings or tissue feedback. Examples of waveforms include high crest factor RF electrical signal waveforms for surface tissue coagulation, low crest factor RF electrical signal waveform for deeper tissue penetration, and electrical signal waveforms that promote efficient touch-up coagulation.
  • the DDS circuit 4200 can create multiple wave shape lookup tables 4210 and during a tissue treatment procedure (e.g.,“on-the-fly” or in virtual real time based on user or sensor inputs) switch between different wave shapes stored in different lookup tables 4210 based on the tissue effect desired and/or tissue feedback.
  • a tissue treatment procedure e.g.,“on-the-fly” or in virtual real time based on user or sensor inputs
  • the lookup tables 4210 can store electrical signal waveforms shaped to maximize the power delivered into the tissue per cycle (i.e. , trapezoidal or square wave). In other aspects, the lookup tables 4210 can store wave shapes synchronized in such way that they make maximizing power delivery by any one of the surgical instruments of surgical system 1000 when delivering RF and ultrasonic drive signals. In yet other aspects, the lookup tables 4210 can store electrical signal waveforms to drive ultrasonic and RF therapeutic, and/or sub-therapeutic, energy simultaneously while maintaining ultrasonic frequency lock.
  • the output wave shape may be in the form of a sine wave, cosine wave, pulse wave, square wave, and the like.
  • the more complex and custom wave shapes specific to different instruments and their tissue effects can be stored in the non-volatile memory of the generator circuit or in the non-volatile memory (e.g., EEPROM) of the surgical instrument and be fetched upon connecting the surgical instrument to the generator circuit.
  • EEPROM non-volatile memory
  • One example of a custom wave shape is an exponentially damped sinusoid as used in many high crest factor “coagulation” waveforms, as shown in FIG. 37.
  • FIG. 37 illustrates one cycle of a discrete time digital electrical signal waveform 4300, in accordance with at least one aspect of the present disclosure of an analog waveform 4304 (shown superimposed over the discrete time digital electrical signal waveform 4300 for comparison purposes).
  • the horizontal axis represents Time (t) and the vertical axis represents digital phase points.
  • the digital electrical signal waveform 4300 is a digital discrete time version of the desired analog waveform 4304, for example.
  • the digital electrical signal waveform 4300 is generated by storing an amplitude phase point 4302 that represents the amplitude per clock cycle T dk over one cycle or period T 0 .
  • the digital electrical signal waveform 4300 is generated over one period T 0 by any suitable digital processing circuit.
  • the amplitude phase points are digital words stored in a memory circuit.
  • the digital word is a six-bit word that is capable of storing the amplitude phase points with a resolution of 26 or 64 bits. It will be appreciated that the examples shown in FIGS. 35 and 36 is for illustrative purposes and in actual implementations the resolution can be much higher.
  • the digital amplitude phase points 4302 over one cycle T 0 are stored in the memory as a string of string words in a lookup table 4104, 4210 as described in connection with FIGS. 35 and 36, for example.
  • the amplitude phase points 4302 are read sequentially from the memory from 0 to T 0 per clock cycle T c ik and are
  • a DAC circuit 4108, 4212 also described in connection with FIGS. 35 and 36. Additional cycles can be generated by repeatedly reading the amplitude phase points 4302 of the digital electrical signal waveform 4300 the from 0 to T 0 for as many cycles or periods as may be desired.
  • the smooth analog version of the analog waveform 4304 is achieved by filtering the output of the DAC circuit 4108, 4212 by a filter 41 12, 4214 (FIGS. 35 and 36).
  • the filtered analog output signal 41 14, 4222 (FIGS. 35 and 36) is applied to the input of a power amplifier.
  • FIG. 38 is a diagram of a control system 12950 configured to provide progressive closure of a closure member (e.g., closure tube) when the displacement member advances distally and couples into a clamp arm (e.g., anvil) to lower the closure force load on the closure member at a desired rate and decrease the firing force load on the firing member according to one aspect of this disclosure.
  • the control system 12950 may be implemented as a nested PID feedback controller.
  • a PID controller is a control loop feedback mechanism (controller) to continuously calculate an error value as the difference between a desired set point and a measured process variable and applies a correction based on proportional, integral, and derivative terms (sometimes denoted P, I, and D respectively).
  • the nested PID controller feedback control system 12950 includes a primary controller 12952, in a primary (outer) feedback loop 12954 and a secondary controller 12955 in a secondary (inner) feedback loop 12956.
  • the primary controller 12952 may be a PID controller 12972 as shown in FIG. 39, and the secondary controller 12955 also may be a PID controller 12972 as shown in FIG. 39.
  • the primary controller 12952 controls a primary process 12958 and the secondary controller 12955 controls a secondary process 12960.
  • the output 12966 of the primary process 12958 is subtracted from a primary set point SPi by a first summer 12962.
  • the first summer 12962 produces a single sum output signal which is applied to the primary controller 12952.
  • the output of the primary controller 12952 is the secondary set point SP 2 .
  • the output 12968 of the secondary process 12960 is subtracted from the secondary set point SP 2 by a second summer 12964.
  • the control system 12950 may be configured such that the primary set point SPi is a desired closure force value and the primary controller 12952 is configured to receive the closure force from a torque sensor coupled to the output of a closure motor and determine a set point SP 2 motor velocity for the closure motor.
  • the closure force may be measured with strain gauges, load cells, or other suitable force sensors.
  • the closure motor velocity set point SP 2 is compared to the actual velocity of the closure tube, which is determined by the secondary controller 12955.
  • the actual velocity of the closure tube may be measured by comparing measuring the displacement of the closure tube with the position sensor and measuring elapsed time with a timer/counter.
  • the output 12968 of the secondary process 12960 is the actual velocity of the closure tube.
  • This closure tube velocity output 12968 is provided to the primary process 12958 which determines the force acting on the closure tube and is fed back to the adder 12962, which subtracts the measured closure force from the primary set point SPi .
  • the primary set point SPi may be an upper threshold or a lower threshold.
  • the primary controller 12952 controls the velocity and direction of the closure motor.
  • the secondary controller 12955 controls the velocity of the closure motor based on the actual velocity of closure tube measured by the secondary process 12960 and the secondary set point SP 2 , which is based on a comparison of the actual firing force and the firing force upper and lower thresholds.
  • FIG. 39 illustrates a PID feedback control system 12970 according to one aspect of this disclosure.
  • the primary controller 12952 or the secondary controller 12955, or both, may be implemented as a PID controller 12972.
  • the PID controller 12972 may comprise a proportional element 12974 (P), an integral element 12976 (I), and a derivative element 12978 (D).
  • P proportional element 12974
  • I integral element 12976
  • D derivative element 12978
  • the outputs of the P, I, D elements 12974, 12976, 12978 are summed by a summer 12986, which provides the control variable m( ⁇ ) to the process 12980.
  • the output of the process 12980 is the process variable y(t).
  • a summer 12984 calculates the difference between a desired set point r(t) and a measured process variable y(t).
  • the PID controller 12972 continuously calculates an error value e(t) (e.g., difference between closure force threshold and measured closure force) as the difference between a desired set point r(t) (e.g., closure force threshold) and a measured process variable y(t) (e.g., velocity and direction of closure tube) and applies a correction based on the proportional, integral, and derivative terms calculated by the
  • proportional element 12974 P
  • integral element 12976 I
  • derivative element 12978 D
  • the PID controller 12972 attempts to minimize the error eft) over time by adjustment of the control variable m( ⁇ ) (e.g., velocity and direction of the closure tube).
  • the“P” element 12974 accounts for present values of the error. For example, if the error is large and positive, the control output will also be large and positive. In accordance with the present disclosure, the error term eft) is the different between the desired closure force and the measured closure force of the closure tube.
  • the ⁇ ” element 12976 accounts for past values of the error. For example, if the current output is not sufficiently strong, the integral of the error will accumulate over time, and the controller will respond by applying a stronger action.
  • The“D” element 12978 accounts for possible future trends of the error, based on its current rate of change.
  • the large positive control output succeeds in bringing the error closer to zero, it also puts the process on a path to large negative error in the near future.
  • the derivative turns negative and the D module reduces the strength of the action to prevent this overshoot.
  • the adaptive closure member velocity control algorithm described herein may measure at least two of the following parameters: firing member stroke location, firing member load, displacement of cutting element, velocity of cutting element, closure tube stroke location, closure tube load, among others.
  • Ultrasonic surgical devices such as ultrasonic scalpels, are finding increasingly widespread applications in surgical procedures by virtue of their unique performance characteristics. Depending upon specific device configurations and operational parameters, ultrasonic surgical devices can provide substantially simultaneous transection of tissue and homeostasis by coagulation, desirably minimizing patient trauma.
  • An ultrasonic surgical device may comprise a handpiece containing an ultrasonic transducer, and an instrument coupled to the ultrasonic transducer having a distally-mounted end effector (e.g., a blade tip) to cut and seal tissue.
  • the instrument may be permanently affixed to the handpiece. In other cases, the instrument may be detachable from the handpiece, as in the case of a disposable instrument or an interchangeable instrument.
  • the end effector transmits ultrasonic energy to tissue brought into contact with the end effector to realize cutting and sealing action.
  • Ultrasonic surgical devices of this nature can be configured for open surgical use, laparoscopic, or endoscopic surgical procedures including robotic-assisted procedures.
  • Ultrasonic energy cuts and coagulates tissue using temperatures lower than those used in electrosurgical procedures and can be transmitted to the end effector by an ultrasonic generator in communication with the handpiece. Vibrating at high frequencies (e.g., 55,500 cycles per second), the ultrasonic blade denatures protein in the tissue to form a sticky coagulum. Pressure exerted on tissue by the blade surface collapses blood vessels and allows the coagulum to form a hemostatic seal. A surgeon can control the cutting speed and coagulation by the force applied to the tissue by the end effector, the time over which the force is applied, and the selected excursion level of the end effector.
  • high frequencies e.g., 55,500 cycles per second
  • the ultrasonic transducer may be modeled as an equivalent circuit comprising a first branch having a static capacitance and a second“motional” branch having a serially connected inductance, resistance and capacitance that define the electromechanical properties of a resonator.
  • Known ultrasonic generators may include a tuning inductor for tuning out the static capacitance at a resonant frequency so that substantially all of a generator’s drive signal current flows into the motional branch. Accordingly, by using a tuning inductor, the generator’s drive signal current represents the motional branch current, and the generator is thus able to control its drive signal to maintain the ultrasonic transducer’s resonant frequency.
  • the tuning inductor may also transform the phase impedance plot of the ultrasonic transducer to improve the generator’s frequency lock capabilities.
  • the tuning inductor must be matched with the specific static capacitance of an ultrasonic transducer at the operational resonant frequency. In other words, a different ultrasonic transducer having a different static capacitance requires a different tuning inductor.
  • the generator’s drive signal exhibits asymmetrical harmonic distortion that complicates impedance magnitude and phase measurements. For example, the accuracy of impedance phase measurements may be reduced due to harmonic distortion in the current and voltage signals.
  • Electrosurgical devices for applying electrical energy to tissue in order to treat and/or destroy the tissue are also finding increasingly widespread applications in surgical procedures.
  • An electrosurgical device may comprise a handpiece and an instrument having a distally- mounted end effector (e.g., one or more electrodes). The end effector can be positioned against the tissue such that electrical current is introduced into the tissue.
  • Electrosurgical devices can be configured for bipolar or monopolar operation. During bipolar operation, current is introduced into and returned from the tissue by active and return electrodes, respectively, of the end effector. During monopolar operation, current is introduced into the tissue by an active electrode of the end effector and returned through a return electrode (e.g., a grounding pad) separately located on a patient’s body.
  • a return electrode e.g., a grounding pad
  • Heat generated by the current flowing through the tissue may form hemostatic seals within the tissue and/or between tissues and thus may be particularly useful for sealing blood vessels, for example.
  • the end effector of an electrosurgical device may also comprise a cutting member that is movable relative to the tissue and the electrodes to transect the tissue.
  • RF energy is a form of electrical energy that may be in the frequency range of 300 kHz to 1 MHz, as described in EN60601-2-2:2009+A1 1 :201 1 , Definition 201 .3.218 - HIGH FREQUENCY.
  • RF energy is typically restricted to less than 5MHz.
  • the frequency can be almost any value. Frequencies above 200 kHz are typically used for monopolar applications in order to avoid the unwanted stimulation of nerves and muscles which would result from the use of low frequency current.
  • Lower frequencies may be used for bipolar techniques if a risk analysis shows the possibility of neuromuscular stimulation has been mitigated to an acceptable level. Normally, frequencies above 5 MHz are not used in order to minimize the problems associated with high frequency leakage currents. It is generally recognized that 10 mA is the lower threshold of thermal effects on tissue.
  • an electrosurgical device can transmit low frequency RF energy through tissue, which causes ionic agitation, or friction, in effect resistive heating, thereby increasing the temperature of the tissue. Because a sharp boundary may be created between the affected tissue and the surrounding tissue, surgeons can operate with a high level of precision and control, without sacrificing un-targeted adjacent tissue.
  • the low operating temperatures of RF energy may be useful for removing, shrinking, or sculpting soft tissue while simultaneously sealing blood vessels.
  • RF energy may work particularly well on connective tissue, which is primarily comprised of collagen and shrinks when contacted by heat.
  • ultrasonic and electrosurgical devices Due to their unique drive signal, sensing and feedback needs, ultrasonic and electrosurgical devices have generally required different generators. Additionally, in cases where the instrument is disposable or interchangeable with a handpiece, ultrasonic and electrosurgical generators are limited in their ability to recognize the particular instrument configuration being used and to optimize control and diagnostic processes accordingly.
  • capacitive coupling between the non-isolated and patient-isolated circuits of the generator may result in exposure of a patient to unacceptable levels of leakage current.
  • ultrasonic and electrosurgical devices have generally required different user interfaces for the different generators.
  • one user interface is configured for use with an ultrasonic instrument whereas a different user interface may be configured for use with an electrosurgical instrument.
  • Such user interfaces include hand and/or foot activated user interfaces such as hand activated switches and/or foot activated switches.
  • additional user interfaces that are configured to operate with both ultrasonic and/or electrosurgical instrument generators also are contemplated.
  • Additional user interfaces for providing feedback, whether to the user or other machine, are contemplated within the subsequent disclosure to provide feedback indicating an operating mode or status of either an ultrasonic and/or electrosurgical instrument.
  • Providing user and/or machine feedback for operating a combination ultrasonic and/or electrosurgical instrument will require providing sensory feedback to a user and electrical/mechanical/electro-mechanical feedback to a machine.
  • Feedback devices that incorporate visual feedback devices (e.g., an LCD display screen, LED indicators), audio feedback devices (e.g., a speaker, a buzzer) or tactile feedback devices (e.g., haptic actuators) for use in combined ultrasonic and/or electrosurgical instruments are contemplated in the subsequent disclosure.
  • ultrasonic surgical devices can be configured for transecting and/or coagulating tissue during surgical procedures, for example.
  • Aspects of the electrosurgical devices can be configured for transecting, coagulating, scaling, welding and/or desiccating tissue during surgical procedures, for example.
  • aspects of the generator utilize high-speed analog-to-digital sampling (e.g., approximately 200* oversampling, depending on frequency) of the generator drive signal current and voltage, along with digital signal processing, to provide a number of advantages and benefits over known generator architectures.
  • the generator may determine the motional branch current of an ultrasonic transducer. This provides the benefit of a virtually tuned system, and simulates the presence of a system that is tuned or resonant with any value of the static capacitance (e.g., C 0 in FIG. 25) at any frequency.
  • control of the motional branch current may be realized by tuning out the effects of the static capacitance without the need for a tuning inductor. Additionally, the elimination of the tuning inductor may not degrade the generator’s frequency lock capabilities, as frequency lock can be realized by suitably processing the current and voltage feedback data.
  • High-speed analog-to-digital sampling of the generator drive signal current and voltage, along with digital signal processing, may also enable precise digital filtering of the samples.
  • aspects of the generator may utilize a low-pass digital filter (e.g., a finite impulse response (FIR) filter) that rolls off between a fundamental drive signal frequency and a second-order harmonic to reduce the asymmetrical harmonic distortion and EMI-induced noise in current and voltage feedback samples.
  • the filtered current and voltage feedback samples represent substantially the fundamental drive signal frequency, thus enabling a more accurate impedance phase measurement with respect to the fundamental drive signal frequency and an improvement in the generator’s ability to maintain resonant frequency lock.
  • the accuracy of the impedance phase measurement may be further enhanced by averaging falling edge and rising edge phase measurements, and by regulating the measured impedance phase to 0°.
  • Various aspects of the generator may also utilize the high-speed analog-to-digital sampling of the generator drive signal current and voltage, along with digital signal processing, to determine real power consumption and other quantities with a high degree of precision.
  • This may allow the generator to implement a number of useful algorithms, such as, for example, controlling the amount of power delivered to tissue as the impedance of the tissue changes and controlling the power delivery to maintain a constant rate of tissue impedance increase.
  • Some of these algorithms are used to determine the phase difference between the generator drive signal current and voltage signals. At resonance, the phase difference between the current and voltage signals is zero. The phase changes as the ultrasonic system goes off-resonance.
  • phase information may be used to infer the conditions of the ultrasonic blade. As discussed with particularity below, the phase changes as a function of the temperature of the ultrasonic blade. Therefore, the phase information may be employed to control the temperature of the ultrasonic blade. This may be done, for example, by reducing the power delivered to the ultrasonic blade when the ultrasonic blade runs too hot and increasing the power delivered to the ultrasonic blade when the ultrasonic blade runs too cold.
  • Various aspects of the generator may have a wide frequency range and increased output power necessary to drive both ultrasonic surgical devices and electrosurgical devices.
  • the lower voltage, higher current demand of electrosurgical devices may be met by a dedicated tap on a wideband power transformer, thereby eliminating the need for a separate power amplifier and output transformer.
  • sensing and feedback circuits of the generator may support a large dynamic range that addresses the needs of both ultrasonic and electrosurgical applications with minimal distortion.
  • Various aspects may provide a simple, economical means for the generator to read from, and optionally write to, a data circuit (e.g., a single-wire bus device, such as a one-wire protocol EEPROM known under the trade name“1 -Wire”) disposed in an instrument attached to the handpiece using existing multi-conductor generator/handpiece cables.
  • a data circuit e.g., a single-wire bus device, such as a one-wire protocol EEPROM known under the trade name“1 -Wire”
  • the generator is able to retrieve and process instrument-specific data from an instrument attached to the handpiece. This may enable the generator to provide better control and improved diagnostics and error detection.
  • the ability of the generator to write data to the instrument makes possible new functionality in terms of, for example, tracking instrument usage and capturing operational data.
  • the use of frequency band permits the backward compatibility of instruments containing a bus device with existing generators.
  • Disclosed aspects of the generator provide active cancellation of leakage current caused by unintended capacitive coupling between non-isolated and patient-isolated circuits of the generator. In addition to reducing patient risk, the reduction of leakage current may also lessen electromagnetic emissions.
  • FIG. 40 is a system diagram 7400 of a segmented circuit 7401 comprising a plurality of independently operated circuit segments 7402, 7414, 7416, 7420, 7424, 7428, 7434, 7440, in accordance with at least one aspect of the present disclosure.
  • a circuit segment of the plurality of circuit segments of the segmented circuit 7401 comprises one or more circuits and one or more sets of machine executable instructions stored in one or more memory devices.
  • the one or more circuits of a circuit segment are coupled to for electrical communication through one or more wired or wireless connection media.
  • the plurality of circuit segments are configured to transition between three modes comprising a sleep mode, a standby mode and an operational mode.
  • the plurality of circuit segments 7402, 7414, 7416, 7420, 7424, 7428, 7434, 7440 start first in the standby mode, transition second to the sleep mode, and transition third to the operational mode.
  • the plurality of circuit segments may transition from any one of the three modes to any other one of the three modes.
  • the plurality of circuit segments may transition directly from the standby mode to the operational mode.
  • Individual circuit segments may be placed in a particular state by the voltage control circuit 7408 based on the execution by a processor of machine executable instructions.
  • the states comprise a deenergized state, a low energy state, and an energized state.
  • the deenergized state corresponds to the sleep mode
  • the low energy state corresponds to the standby mode
  • the plurality of circuit segments 7402, 7414, 7416, 7420, 7424, 7428, 7434, 7440 may transition from the sleep mode or the standby mode to the operational mode in accordance with an energization sequence.
  • the plurality of circuit segments also may transition from the operational mode to the standby mode or the sleep mode in accordance with a deenergization sequence.
  • the energization sequence and the deenergization sequence may be different.
  • the energization sequence comprises energizing only a subset of circuit segments of the plurality of circuit segments.
  • the deenergization sequence comprises deenergizing only a subset of circuit segments of the plurality of circuit segments.
  • the segmented circuit 7401 comprise a plurality of circuit segments comprising a transition circuit segment 7402, a processor circuit segment 7414, a handle circuit segment 7416, a communication circuit segment 7420, a display circuit segment 7424, a motor control circuit segment 7428, an energy treatment circuit segment 7434, and a shaft circuit segment 7440.
  • the transition circuit segment comprises a wake up circuit 7404, a boost current circuit 7406, a voltage control circuit 7408, a safety controller 7410 and a POST controller 7412.
  • the transition circuit segment 7402 is configured to implement a deenergization and an energization sequence, a safety detection protocol, and a POST.
  • the wake up circuit 7404 comprises an accelerometer button sensor 7405.
  • the transition circuit segment 7402 is configured to be in an energized state while other circuit segments of the plurality of circuit segments of the segmented circuit 7401 are configured to be in a low energy state, a deenergized state or an energized state.
  • the accelerometer button sensor 7405 may monitor movement or acceleration of the surgical instrument 6480 described herein.
  • the movement may be a change in orientation or rotation of the surgical instrument.
  • the surgical instrument may be moved in any direction relative to a three dimensional Euclidean space by for example, a user of the surgical instrument.
  • the accelerometer button sensor 7405 When the accelerometer button sensor 7405 senses movement or acceleration, the accelerometer button sensor 7405 sends a signal to the voltage control circuit 7408 to cause the voltage control circuit 7408 to apply voltage to the processor circuit segment 7414 to transition the processor and a volatile memory to an energized state. In aspects, the processor and the volatile memory are in an energized state before the voltage control circuit 7409 applies voltage to the processor and the volatile memory. In the operational mode, the processor may initiate an energization sequence or a deenergization sequence. In various aspects, the accelerometer button sensor 7405 may also send a signal to the processor to cause the processor to initiate an energization sequence or a deenergization sequence.
  • the processor initiates an energization sequence when the majority of individual circuit segments are in a low energy state or a deenergized state. In other aspects, the processor initiates a deenergization sequence when the majority of individual circuit segments are in an energized state.
  • the accelerometer button sensor 7405 may sense external movement within a predetermined vicinity of the surgical instrument.
  • the accelerometer button sensor 7405 may sense a user of the surgical instrument 6480 described herein moving a hand of the user within the predetermined vicinity.
  • the accelerometer button sensor 7405 may send a signal to the voltage control circuit 7408 and a signal to the processor, as previously described.
  • the processor may initiate an energization sequence or a deenergization sequence to transition one or more circuit segments between the three modes.
  • the signal sent to the voltage control circuit 7408 is sent to verify that the processor is in operational mode.
  • the accelerometer button sensor 7405 may sense when the surgical instrument has been dropped and send a signal to the processor based on the sensed drop.
  • the signal can indicate an error in the operation of an individual circuit segment.
  • One or more sensors may sense damage or malfunctioning of the affected individual circuit segments. Based on the sensed damage or malfunctioning, the POST controller 7412 may perform a POST of the corresponding individual circuit segments.
  • An energization sequence or a deenergization sequence may be defined based on the accelerometer button sensor 7405.
  • the accelerometer button sensor 7405 may sense a particular motion or a sequence of motions that indicates the selection of a particular circuit segment of the plurality of circuit segments. Based on the sensed motion or series of sensed motions, the accelerometer button sensor 7405 may transmit a signal comprising an indication of one or more circuit segments of the plurality of circuit segments to the processor when the processor is in an energized state. Based on the signal, the processor determines an energization sequence comprising the selected one or more circuit segments.
  • a user of the surgical instruments 6480 described herein may select a number and order of circuit segments to define an energization sequence or a deenergization sequence based on interaction with a graphical user interface (GUI) of the surgical instrument.
  • GUI graphical user interface
  • the accelerometer button sensor 7405 may send a signal to the voltage control circuit 7408 and a signal to the processor only when the accelerometer button sensor 7405 detects movement of the surgical instrument 6480 described herein or external movement within a predetermined vicinity above a predetermined threshold. For example, a signal may only be sent if movement is sensed for 5 or more seconds or if the surgical instrument is moved 5 or more inches.
  • the accelerometer button sensor 7405 may send a signal to the voltage control circuit 7408 and a signal to the processor only when the accelerometer button sensor 7405 detects oscillating movement of the surgical instrument.
  • the transition may comprise a transition to operational mode according to an energization sequence, a transition to low energy mode according to a deenergization sequence, or a transition to sleep mode according to a deenergization sequence.
  • the surgical instrument comprises an actuator that may be actuated by a user of the surgical instrument. The actuation is sensed by the accelerometer button sensor 7405.
  • the actuator may be a slider, a toggle switch, or a momentary contact switch. Based on the sensed actuation, the accelerometer button sensor 7405 may send a signal to the voltage control circuit 7408 and a signal to the processor.
  • the boost current circuit 7406 is coupled to a battery.
  • the boost current circuit 7406 is a current amplifier, such as a relay or transistor, and is configured to amplify the magnitude of a current of an individual circuit segment.
  • the initial magnitude of the current corresponds to the source voltage provided by the battery to the segmented circuit 7401.
  • Suitable relays include solenoids.
  • Suitable transistors include field-effect transistors (FET), MOSFET, and bipolar junction transistors (BJT).
  • the boost current circuit 7406 may amplify the magnitude of the current corresponding to an individual circuit segment or circuit which requires more current draw during operation of the surgical instruments 6480 described herein.
  • an increase in current to the motor control circuit segment 7428 may be provided when a motor of the surgical instrument requires more input power.
  • the increase in current provided to an individual circuit segment may cause a corresponding decrease in current of another circuit segment or circuit segments.
  • the increase in current may correspond to voltage provided by an additional voltage source operating in conjunction with the battery.
  • the voltage control circuit 7408 is coupled to the battery.
  • the voltage control circuit 7408 is configured to provide voltage to or remove voltage from the plurality of circuit segments.
  • the voltage control circuit 7408 is also configured to increase or reduce voltage provided to the plurality of circuit segments of the segmented circuit 7401 .
  • the voltage control circuit 7408 comprises a combinational logic circuit such as a multiplexer (MUX) to select inputs, a plurality of electronic switches, and a plurality of voltage converters.
  • MUX multiplexer
  • An electronic switch of the plurality of electronic switches may be configured to switch between an open and closed configuration to disconnect or connect an individual circuit segment to or from the battery.
  • the plurality of electronic switches may be solid state devices such as transistors or other types of switches such as wireless switches, ultrasonic switches, accelerometers, inertial sensors, among others.
  • the combinational logic circuit is configured to select an individual electronic switch for switching to an open configuration to enable application of voltage to the corresponding circuit segment.
  • the combination logic circuit also is configured to select an individual electronic switch for switching to a closed configuration to enable removal of voltage from the corresponding circuit segment.
  • the combination logic circuit may implement a deenergization sequence or an energization sequence.
  • the plurality of voltage converters may provide a stepped-up voltage or a stepped- down voltage to the plurality of circuit segments.
  • the voltage control circuit 7408 may also comprise a microprocessor and memory device.
  • the safety controller 7410 is configured to perform safety checks for the circuit segments. In some aspects, the safety controller 7410 performs the safety checks when one or more individual circuit segments are in the operational mode. The safety checks may be performed to determine whether there are any errors or defects in the functioning or operation of the circuit segments.
  • the safety controller 7410 may monitor one or more parameters of the plurality of circuit segments. The safety controller 7410 may verify the identity and operation of the plurality of circuit segments by comparing the one or more parameters with predefined parameters. For example, if an RF energy modality is selected, the safety controller 7410 may verify that an articulation parameter of the shaft matches a predefined articulation parameter to verify the operation of the RF energy modality of the surgical instrument 6480 described herein.
  • the safety controller 7410 may monitor, by the sensors, a predetermined relationship between one or more properties of the surgical instrument to detect a fault.
  • a fault may arise when the one or more properties are inconsistent with the predetermined relationship.
  • the safety controller 7410 determines that a fault exists, an error exists, or that some operation of the plurality of circuit segments was not verified, the safety controller 7410 prevents or disables operation of the particular circuit segment where the fault, error or verification failure originated.
  • the POST controller 7412 performs a POST to verify proper operation of the plurality of circuit segments.
  • the POST is performed for an individual circuit segment of the plurality of circuit segments prior to the voltage control circuit 7408 applying a voltage to the individual circuit segment to transition the individual circuit segment from standby mode or sleep mode to operational mode. If the individual circuit segment does not pass the POST, the particular circuit segment does not transition from standby mode or sleep mode to operational mode.
  • POST of the handle circuit segment 7416 may comprise, for example, testing whether the handle control sensors 7418 sense an actuation of a handle control of the surgical instrument 6480 described herein.
  • the POST controller 7412 may transmit a signal to the accelerometer button sensor 7405 to verify the operation of the individual circuit segment as part of the POST.
  • the accelerometer button sensor 7405 may prompt a user of the surgical instrument to move the surgical instrument to a plurality of varying locations to confirm operation of the surgical instrument.
  • the accelerometer button sensor 7405 may also monitor an output of a circuit segment or a circuit of a circuit segment as part of the POST.
  • the accelerometer button sensor 7405 can sense an incremental motor pulse generated by the motor 7432 to verify operation.
  • a motor controller of the motor control circuit 7430 may be used to control the motor 7432 to generate the incremental motor pulse.
  • the surgical instrument 6480 described herein may comprise additional accelerometer button sensors.
  • the POST controller 7412 may also execute a control program stored in the memory device of the voltage control circuit 7408.
  • the control program may cause the POST controller 7412 to transmit a signal requesting a matching encrypted parameter from a plurality of circuit segments. Failure to receive a matching encrypted parameter from an individual circuit segment indicates to the POST controller 7412 that the corresponding circuit segment is damaged or malfunctioning. In some aspects, if the POST controller 7412 determines based on the POST that the processor is damaged or
  • the POST controller 7412 may send a signal to one or more secondary processors to cause one or more secondary processors to perform critical functions that the processor is unable to perform. In some aspects, if the POST controller 7412 determines based on the POST that one or more circuit segments do not operate properly, the POST controller 7412 may initiate a reduced performance mode of those circuit segments operating properly while locking out those circuit segments that fail POST or do not operate properly. A locked out circuit segment may function similarly to a circuit segment in standby mode or sleep mode.
  • the processor circuit segment 7414 comprises the processor and the volatile memory. The processor is configured to initiate an energization or a deenergization sequence.
  • the processor transmits an energizing signal to the voltage control circuit 7408 to cause the voltage control circuit 7408 to apply voltage to the plurality or a subset of the plurality of circuit segments in accordance with the energization sequence.
  • the processor transmits a deenergizing signal to the voltage control circuit 7408 to cause the voltage control circuit 7408 to remove voltage from the plurality or a subset of the plurality of circuit segments in accordance with the deenergization sequence.
  • the handle circuit segment 7416 comprises handle control sensors 7418.
  • the handle control sensors 7418 may sense an actuation of one or more handle controls of the surgical instrument 6480 described herein.
  • the one or more handle controls comprise a clamp control, a release button, an articulation switch, an energy activation button, and/or any other suitable handle control.
  • the user may activate the energy activation button to select between an RF energy mode, an ultrasonic energy mode or a combination RF and ultrasonic energy mode.
  • the handle control sensors 7418 may also facilitate attaching a modular handle to the surgical instrument.
  • the handle control sensors 7418 may sense proper attachment of the modular handle to the surgical instrument and indicate the sensed attachment to a user of the surgical instrument.
  • the LCD display 7426 may provide a graphical indication of the sensed attachment.
  • the handle control sensors 7418 senses actuation of the one or more handle controls. Based on the sensed actuation, the processor may initiate either an energization sequence or a deenergization sequence.
  • the communication circuit segment 7420 comprises a communication circuit 7422.
  • the communication circuit 7422 comprises a communication interface to facilitate signal communication between the individual circuit segments of the plurality of circuit segments.
  • the communication circuit 7422 provides a path for the modular components of the surgical instrument 6480 described herein to communicate electrically.
  • a modular shaft and a modular transducer when attached together to the handle of the surgical instrument, can upload control programs to the handle through the communication circuit 7422.
  • the display circuit segment 7424 comprises a LCD display 7426.
  • the LCD display 7426 may comprise a liquid crystal display screen, LED indicators, etc.
  • the LCD display 7426 is an organic light-emitting diode (OLED) screen.
  • a display may be placed on, embedded in, or located remotely from the surgical instrument 6480 described herein. For example, the display can be placed on the handle of the surgical instrument.
  • the display is configured to provide sensory feedback to a user.
  • the LCD display 7426 further comprises a backlight.
  • the surgical instrument may also comprise audio feedback devices such as a speaker or a buzzer and tactile feedback devices such as a haptic actuator.
  • the motor control circuit segment 7428 comprises a motor control circuit 7430 coupled to a motor 7432.
  • the motor 7432 is coupled to the processor by a driver and a transistor, such as a FET.
  • the motor control circuit 7430 comprises a motor current sensor in signal communication with the processor to provide a signal indicative of a measurement of the current draw of the motor to the processor.
  • the processor transmits the signal to the display.
  • the display receives the signal and displays the measurement of the current draw of the motor 7432.
  • the processor may use the signal, for example, to monitor that the current draw of the motor 7432 exists within an acceptable range, to compare the current draw to one or more parameters of the plurality of circuit segments, and to determine one or more parameters of a patient treatment site.
  • the motor control circuit 7430 comprises a motor controller to control the operation of the motor.
  • the motor control circuit 7430 controls various motor parameters, such as by adjusting the velocity, torque and acceleration of the motor 7432. The adjusting is done based on the current through the motor 7432 measured by the motor current sensor.
  • the motor control circuit 7430 comprises a force sensor to measure the force and torque generated by the motor 7432.
  • the motor 7432 is configured to actuate a mechanism of the surgical instruments 6480 described herein.
  • the motor 7432 is configured to control actuation of the shaft of the surgical instrument to realize clamping, rotation and articulation functionality.
  • the motor 7432 may actuate the shaft to realize a clamping motion with jaws of the surgical instrument.
  • the motor controller may determine whether the material clamped by the jaws is tissue or metal.
  • the motor controller may also determine the extent to which the jaws clamp the material. For example, the motor controller may determine how open or closed the jaws are based on the derivative of sensed motor current or motor voltage.
  • the motor 7432 is configured to actuate the transducer to cause the transducer to apply torque to the handle or to control articulation of the surgical instrument.
  • the motor current sensor may interact with the motor controller to set a motor current limit. When the current meets the predefined threshold limit, the motor controller initiates a corresponding change in a motor control operation. For example, exceeding the motor current limit causes the motor controller to reduce the current draw of the motor.
  • the energy treatment circuit segment 7434 comprises a RF amplifier and safety circuit 7436 and an ultrasonic signal generator circuit 7438 to implement the energy modular functionality of the surgical instrument 6480 described herein.
  • the RF amplifier and safety circuit 7436 is configured to control the RF modality of the surgical instrument by generating an RF signal.
  • the ultrasonic signal generator circuit 7438 is configured to control the ultrasonic energy modality by generating an ultrasonic signal.
  • the RF amplifier and safety circuit 7436 and an ultrasonic signal generator circuit 7438 may operate in conjunction to control the combination RF and ultrasonic energy modality.
  • the shaft circuit segment 7440 comprises a shaft module controller 7442, a modular control actuator 7444, one or more end effector sensors 7446, and a non volatile memory 7448.
  • the shaft module controller 7442 is configured to control a plurality of shaft modules comprising the control programs to be executed by the processor.
  • the plurality of shaft modules implements a shaft modality, such as ultrasonic, combination ultrasonic and RF, RF l-blade, and RF-opposable jaw.
  • the shaft module controller 7442 can select shaft modality by selecting the corresponding shaft module for the processor to execute.
  • the modular control actuator 7444 is configured to actuate the shaft according to the selected shaft modality.
  • the shaft articulates the end effector according to the one or more parameters, routines or programs specific to the selected shaft modality and the selected end effector modality.
  • the one or more end effector sensors 7446 located at the end effector may include force sensors, temperature sensors, current sensors or motion sensors.
  • the one or more end effector sensors 7446 transmit data about one or more operations of the end effector, based on the energy modality implemented by the end effector.
  • the energy modalities include an ultrasonic energy modality, a RF energy modality, or a combination of the ultrasonic energy modality and the RF energy modality.
  • the non volatile memory 7448 stores the shaft control programs.
  • a control program comprises one or more parameters, routines or programs specific to the shaft.
  • the non volatile memory 7448 may be an ROM, EPROM, EEPROM or flash memory.
  • the non volatile memory 7448 stores the shaft modules
  • the shaft modules may be changed or upgraded in the non volatile memory 7448 by the shaft module controller 7442, depending on the surgical instrument shaft to be used in operation.
  • FIG. 41 is a schematic diagram of a circuit 7925 of various components of a surgical instrument with motor control functions, in accordance with at least one aspect of the present disclosure.
  • the surgical instrument 6480 described herein may include a drive mechanism 7930 which is configured to drive shafts and/or gear components in order to perform the various operations associated with the surgical instrument 6480.
  • the drive mechanism 7930 includes a rotation drivetrain 7932 configured to rotate an end effector, for example, about a longitudinal axis relative to handle housing.
  • the drive mechanism 7930 further includes a closure drivetrain 7934 configured to close a jaw member to grasp tissue with the end effector.
  • the drive mechanism 7930 includes a firing drive train 7936 configured to open and close a clamp arm portion of the end effector to grasp tissue with the end effector.
  • the drive mechanism 7930 includes a selector gearbox assembly 7938 that can be located in the handle assembly of the surgical instrument.
  • a function selection module Proximal to the selector gearbox assembly 7938 is a function selection module which includes a first motor 7942 that functions to selectively move gear elements within the selector gearbox assembly 7938 to selectively position one of the drivetrains 7932, 7934, 7936 into engagement with an input drive component of an optional second motor 7944 and motor drive circuit 7946 (shown in dashed line to indicate that the second motor 7944 and motor drive circuit 7946 are optional components).
  • the motors 7942, 7944 are coupled to motor control circuits 7946, 7948, respectively, which are configured to control the operation of the motors 7942, 7944 including the flow of electrical energy from a power source 7950 to the motors 7942, 7944.
  • the power source 7950 may be a DC battery (e.g., rechargeable lead-based, nickel-based, lithium- ion based, battery etc.) or any other power source suitable for providing electrical energy to the surgical instrument.
  • the surgical instrument further includes a microcontroller 7952 (“controller”).
  • the controller 7952 may include a microprocessor 7954 (“processor”) and one or more computer readable mediums or memory units 7956 (“memory”).
  • the memory 7956 may store various program instructions, which when executed may cause the processor 7954 to perform a plurality of functions and/or calculations described herein.
  • the power source 7950 can be configured to supply power to the controller 7952, for example.
  • the processor 7954 may be in communication with the motor control circuit 7946.
  • the memory 7956 may store program instructions, which when executed by the processor 7954 in response to a user input 7958 or feedback elements 7960, may cause the motor control circuit 7946 to motivate the motor 7942 to generate at least one rotational motion to selectively move gear elements within the selector gearbox assembly 7938 to selectively position one of the drivetrains 7932, 7934, 7936 into engagement with the input drive component of the second motor 7944.
  • the processor 7954 can be in
  • the memory 7956 also may store program instructions, which when executed by the processor 7954 in response to a user input 7958, may cause the motor control circuit 7948 to motivate the motor 7944 to generate at least one rotational motion to drive the drivetrain engaged with the input drive component of the second motor 7948, for example.
  • the controller 7952 and/or other controllers of the present disclosure may be implemented using integrated and/or discrete hardware elements, software elements, and/or a combination of both.
  • integrated hardware elements may include processors, microprocessors, microcontrollers, integrated circuits, ASICs, PLDs, DSPs, FPGAs, logic gates, registers, semiconductor devices, chips, microchips, chip sets, microcontrollers, system on a chip (SoC), and/or single in-line package (SIP).
  • Examples of discrete hardware elements may include circuits and/or circuit elements such as logic gates, field effect transistors, bipolar transistors, resistors, capacitors, inductors, and/or relays.
  • the controller 7952 may include a hybrid circuit comprising discrete and integrated circuit elements or components on one or more substrates, for example.
  • the controller 7952 and/or other controllers of the present disclosure may be an LM 4F230H5QR, available from Texas Instruments, for example.
  • the Texas Instruments LM4F230H5QR is an ARM Cortex-M4F Processor Core comprising on-chip memory of 256 KB single-cycle flash memory, or other non-volatile memory, up to 40 MHz, a prefetch buffer to improve performance above 40 MHz, a 32 KB single-cycle SRAM, internal ROM loaded with StellarisWare® software, 2KB EEPROM, one or more PWM modules, one or more QEI analog, one or more 12-bit ADC with 12 analog input channels, among other features that are readily available.
  • Other microcontrollers may be readily substituted for use with the present disclosure. Accordingly, the present disclosure should not be limited in this context.
  • one or more of the various steps described herein can be performed by a finite state machine comprising either a combinational logic circuit or a sequential logic circuit, where either the combinational logic circuit or the sequential logic circuit is coupled to at least one memory circuit.
  • the at least one memory circuit stores a current state of the finite state machine.
  • the combinational or sequential logic circuit is configured to cause the finite state machine to the steps.
  • the sequential logic circuit may be synchronous or asynchronous.
  • one or more of the various steps described herein can be performed by a circuit that includes a combination of the processor 7958 and the finite state machine, for example.
  • a surgical instrument can be configured to perform self-assessments to determine the state, e.g. health, of the drive mechanism and it various components.
  • the self-assessment can be used to determine when the surgical instrument is capable of performing its function before a re-sterilization or when some of the components should be replaced and/or repaired.
  • Assessment of the drive mechanism and its components including but not limited to the rotation drivetrain 7932, the closure drivetrain 7934, and/or the firing drivetrain 7936, can be accomplished in a variety of ways.
  • the magnitude of deviation from a predicted performance can be used to determine the likelihood of a sensed failure and the severity of such failure.
  • Several metrics can be used including: Periodic analysis of repeatably predictable events, Peaks or drops that exceed an expected threshold, and width of the failure.
  • a signature waveform of a properly functioning drive mechanism or one or more of its components can be employed to assess the state of the drive mechanism or the one or more of its components.
  • One or more vibration sensors can be arranged with respect to a properly functioning drive mechanism or one or more of its components to record various vibrations that occur during operation of the properly functioning drive mechanism or the one or more of its components. The recorded vibrations can be employed to create the signature waveform. Future waveforms can be compared against the signature waveform to assess the state of the drive mechanism and its components.
  • the surgical instrument 7930 includes a drivetrain failure detection module 7962 configured to record and analyze one or more acoustic outputs of one or more of the drivetrains 7932, 7934, 7936.
  • the processor 7954 can be in communication with or otherwise control the module 7962.
  • the module 7962 can be embodied as various means, such as circuitry, hardware, a computer program product comprising a computer readable medium (for example, the memory 7956) storing computer readable program instructions that are executable by a processing device (for example, the processor 7954), or some combination thereof.
  • the processor 36 can include, or otherwise control the module 7962.
  • FIG. 42 is an alternative system 132000 for controlling the frequency of an ultrasonic electromechanical system 132002 and detecting the impedance thereof, in accordance with at least one aspect of the present disclosure.
  • the system 132000 may be incorporated into a generator.
  • a processor 132004 coupled to a memory 132026 programs a programmable counter 132006 to tune to the output frequency f 0 of the ultrasonic electromechanical system 132002.
  • the input frequency is generated by a crystal oscillator 132008 and is input into a fixed counter 132010 to scale the frequency to a suitable value.
  • the outputs of the fixed counter 132010 and the programmable counter 132006 are applied to a phase/frequency detector 132012.
  • the output of the phase/frequency detector 132012 is applied to an amplifier/active filter circuit 132014 to generate a tuning voltage 1 ⁇ 2 that is applied to a voltage controlled oscillator 132016 (VCO).
  • VCO 132016 applies the output frequency f 0 to an ultrasonic transducer portion of the ultrasonic electromechanical system 132002, shown here modeled as an equivalent electrical circuit.
  • the voltage and current signals applied to the ultrasonic transducer are monitored by a voltage sensor 132018 and a current sensor 132020.
  • the outputs of the voltage and current sensors 132018, 13020 are applied to another phase/frequency detector 132022 to determine the phase angle between the voltage and current as measured by the voltage and current sensors 132018, 13020.
  • the output of the phase/frequency detector 132022 is applied to one channel of a high speed analog to digital converter 132024 (ADC) and is provided to the processor 132004 therethrough.
  • ADC analog to digital converter
  • the outputs of the voltage and current sensors 132018, 132020 may be applied to respective channels of the two-channel ADC 132024 and provided to the processor 132004 for zero crossing, FFT, or other algorithm described herein for determining the phase angle between the voltage and current signals applied to the ultrasonic electromechanical system 132002.
  • the tuning voltage V t which is proportional to the output frequency f 0 , may be fed back to the processor 132004 via the ADC 132024.
  • This provides the processor 132004 with a feedback signal proportional to the output frequency f 0 and can use this feedback to adjust and control the output frequency f 0 .
  • FIGS. 43A-43B are graphical representations 133000, 133010 of complex impedance spectra of the same ultrasonic device with a cold (room temperature) and hot ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • a cold ultrasonic blade refers to an ultrasonic blade at room temperature
  • a hot ultrasonic blade refers to an ultrasonic blade after it is frictionally heated in use.
  • FIG. 43A is a graphical representation 133000 of impedance phase angle f as a function of resonant frequency f 0 of the same ultrasonic device with a cold and hot ultrasonic blade and FIG.
  • 43B is a graphical representation 133010 of impedance magnitude
  • are at a minimum at the resonant frequency f 0 .
  • the ultrasonic transducer impedance Z g (t) can be measured as the ratio of the drive signal generator voltage V g (t) and current l g (t) drive signals:
  • the electromechanical resonant frequency f 0 of the ultrasonic device is approximately 55,500 Hz and the excitation frequency of the ultrasonic transducer is set to 55,500 Hz.
  • the phase angle f is at minimum or approximately 0 Rad as indicated by the cold blade plot 133002.
  • is 800 W, e.g., the impedance magnitude
  • the electromechanical resonant frequency f 0 ’ of the ultrasonic device decreases. Since the ultrasonic transducer is still driven by generator voltage V g (t) and generator current l g (t) signals at the previous (cold blade) electromechanical resonant frequency f 0 of 55,500 Hz, the ultrasonic device operates off- resonance fJ causing a shift in the phase angle f between the generator voltage V g (t) and generator current l g (t) signals. There is also an increase in impedance magnitude
  • an electromechanical ultrasonic system includes an ultrasonic transducer, a waveguide, and an ultrasonic blade.
  • the ultrasonic transducer may be modeled as an equivalent series resonant circuit (see FIG. 25) comprising first branch having a static capacitance and a second“motional” branch having a serially connected inductance, resistance and capacitance that define the electromechanical properties of a resonator.
  • the electromechanical ultrasonic system has an initial electromechanical resonant frequency defined by the physical properties of the ultrasonic transducer, the waveguide, and the ultrasonic blade.
  • the ultrasonic transducer is excited by an alternating voltage V g (t) and current l g (t) signal at a frequency equal to the electromechanical resonant frequency, e.g., the resonant frequency of the electromechanical ultrasonic system.
  • V g (t) and current l g (t) signal at a frequency equal to the electromechanical resonant frequency, e.g., the resonant frequency of the electromechanical ultrasonic system.
  • the analogous inductive impedance of the electromechanical ultrasonic system is equal to the analogous capacitive impedance of the electromechanical ultrasonic system.
  • the compliance of the ultrasonic blade modeled as an analogous capacitance
  • the resonant frequency of the electromechanical ultrasonic system decreases as the temperature of the ultrasonic blade increases.
  • the analogous inductive impedance of the electromechanical ultrasonic system is no longer equal to the analogous capacitive impedance of the electromechanical ultrasonic system causing a mismatch between the drive frequency and the new resonant frequency of the
  • the electromechanical ultrasonic system operates“off-resonance.”
  • the mismatch between the drive frequency and the resonant frequency is manifested as a phase angle f between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer.
  • the generator electronics can easily monitor the phase angle f between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer.
  • the phase angle f may be determined through Fourier analysis, weighted least-squares estimation, Kalman filtering, space-vector-based techniques, zero-crossing method, Lissajous figures, three-voltmeter method, crossed-coil method, vector voltmeter and vector impedance methods, phase standard instruments, phase-locked loops, among other techniques previously described.
  • the generator can continuously monitor the phase angle f and adjust the drive frequency until the phase angle f goes to zero. At this point, the new drive frequency is equal to the new resonant frequency of the electromechanical ultrasonic system.
  • the change in phase angle f and/or generator drive frequency can be used as an indirect or inferred measurement of the temperature of the ultrasonic blade.
  • One aspect of estimating or inferring the temperature of an ultrasonic blade may include three steps. First, define a state space model of temperature and frequency that is time and energy dependent. To model temperature as a function of frequency content, a set of non linear state space equations are used to model the relationship between the electromechanical resonant frequency and the temperature of the ultrasonic blade. Second, apply a Kalman filter to improve the accuracy of the temperature estimator and state space model over time. Third, a state estimator is provided in the feedback loop of the Kalman filter to control the power applied to the ultrasonic transducer, and hence the ultrasonic blade, to regulate the temperature of the ultrasonic blade. The three steps are described hereinbelow.
  • the first step is to define a state space model of temperature and frequency that is time and energy dependent.
  • a set of non-linear state space equations are used to model the relationship between the
  • the state space model is given by:
  • the state space model represents the rate of change of the natural frequency of the electromechanical ultrasonic system F n and the rate of change of the temperature ⁇ of the ultrasonic blade with respect to natural frequency F n (t), temperature T(t), energy E(t), and time t.
  • y represents the observability of variables that are measurable and observable such as the natural frequency F n (t) of the electromechanical ultrasonic system, the temperature T(t) of the ultrasonic blade, the energy E(t) applied to the ultrasonic blade, and time t.
  • the temperature T(t) of the ultrasonic blade is observable as an estimate.
  • the second step is to apply a Kalman filter to improve temperature estimator and state space model.
  • FIG. 44 is a diagram of a Kalman filter 133020 to improve the temperature estimator and state space model based on impedance according to the equation:
  • the Kalman filter 133020 may be employed to improve the performance of the temperature estimate and allows for the augmentation of external sensors, models, or prior information to improve temperature prediction in the midst of noisy data.
  • the Kalman filter 133020 includes a regulator 133022 and a plant 133024.
  • a plant 133024 is the combination of process and actuator.
  • a plant 133024 may be referred to with a transfer function which indicates the relation between an input signal and the output signal of a system.
  • the regulator 133022 includes a state estimator 133026 and a controller K 133028.
  • the state regulator 133026 includes a feedback loop 133030.
  • the state regulator 133026 receives y, the output of the plant 133024, as an input and a feedback variable u.
  • the state estimator 133026 is an internal feedback system that converges to the true value of the state of the system.
  • the output of the state estimator 133026 is x, the full feedback control variable including F n (t) of the electromechanical ultrasonic system, the estimate of the temperature T(t) of the ultrasonic blade, the energy E(t ) applied to the ultrasonic blade, the phase angle f, and time t.
  • the input into the controller K 133028 is x and the output of the controller K 133028 u is fed back to the state estimator 133026 and t of the plant 133024.
  • Kalman filtering also known as linear quadratic estimation (LQE) is an algorithm that uses a series of measurements observed over time, containing statistical noise and other inaccuracies, and produces estimates of unknown variables that tend to be more accurate than those based on a single measurement alone, by estimating a joint probability distribution over the variables for each timeframe and thus calculating the maximum likelihood estimate of actual measurements.
  • the algorithm works in a two-step process. In a prediction step, the Kalman filter 133020 produces estimates of the current state variables, along with their uncertainties. Once the outcome of the next measurement (necessarily corrupted with some amount of error, including random noise) is observed, these estimates are updated using a weighted average, with more weight being given to estimates with higher certainty.
  • the algorithm is recursive and can run in real time, using only the present input measurements and the previously calculated state and its uncertainty matrix; no additional past information is required.
  • the Kalman filter 133020 uses a dynamics model of the electromechanical ultrasonic system, known control inputs to that system, and multiple sequential measurements
  • observation of the natural frequency and phase angle of the applied signals (e.g., magnitude and phase of the electrical impedance of the ultrasonic transducer) to the ultrasonic transducer to form an estimate of the varying quantities of the electromechanical ultrasonic system (its state) to predict the temperature of the ultrasonic blade portion of the electromechanical ultrasonic system that is better than an estimate obtained using only one measurement alone.
  • observations of the natural frequency and phase angle of the applied signals (e.g., magnitude and phase of the electrical impedance of the ultrasonic transducer) to the ultrasonic transducer to form an estimate of the varying quantities of the electromechanical ultrasonic system (its state) to predict the temperature of the ultrasonic blade portion of the electromechanical ultrasonic system that is better than an estimate obtained using only one measurement alone.
  • the Kalman filter 133020 is an algorithm that includes sensor and data fusion to provide the maximum likelihood estimate of the temperature of the ultrasonic blade.
  • the Kalman filter 133020 deals effectively with uncertainty due to noisy measurements of the applied signals to the ultrasonic transducer to measure the natural frequency and phase shift data and also deals effectively with uncertainty due to random external factors.
  • the Kalman filter 133020 produces an estimate of the state of the electromechanical ultrasonic system as an average of the predicted state of the system and of the new measurement using a weighted average. Weighted values provide better (i.e., smaller) estimated uncertainty and are more “trustworthy” than unweighted values
  • the weights may be calculated from the covariance, a measure of the estimated uncertainty of the prediction of the system’s state.
  • the result of the weighted average is a new state estimate that lies between the predicted and measured state, and has a better estimated uncertainty than either alone.
  • Kalman filter 133020 requires only the last“best guess,” rather than the entire history, of the state of the electromechanical ultrasonic system to calculate a new state.
  • the relative certainty of the measurements and current state estimate is an important consideration, and it is common to discuss the response of the filter in terms of the gain K of the Kalman filter 133020.
  • the Kalman gain K is the relative weight given to the measurements and current state estimate, and can be“tuned” to achieve particular performance. With a high gain K, the Kalman filter 133020 places more weight on the most recent measurements, and thus follows them more responsively. With a low gain K, the Kalman filter 133020 follows the model predictions more closely. At the extremes, a high gain close to one will result in a more jumpy estimated trajectory, while low gain close to zero will smooth out noise but decrease the responsiveness.
  • the state estimate and covariances are coded into matrices to handle the multiple dimensions involved in a single set of calculations. This allows for a representation of linear relationships between different state variables (such as position, velocity, and acceleration) in any of the transition models or covariances.
  • state variables such as position, velocity, and acceleration
  • Using a Kalman filter 133020 does not assume that the errors are Gaussian. However, the Kalman filter 133020 yields the exact conditional probability estimate in the special case that all errors are Gaussian-distributed.
  • the third step uses a state estimator 133026 in the feedback loop 133032 of the Kalman filter 133020 for control of power applied to the ultrasonic transducer, and hence the ultrasonic blade, to regulate the temperature of the ultrasonic blade.
  • FIG. 45 is a graphical depiction 133040 of three probability distributions employed by the state estimator 133026 of the Kalman filter 133020 shown in FIG. 44 to maximize estimates, in accordance with at least one aspect of the present disclosure.
  • the probability distributions include the prior probability distribution 133042, the prediction (state) probability distribution 133044, and the observation probability distribution 133046.
  • the three probability distributions 133042, 133044, 1330467 are used in feedback control of power applied to an ultrasonic transducer to regulate temperature based on impedance across the ultrasonic transducer measured at a variety of frequencies, in accordance with at least one aspect of the present disclosure.
  • the estimator used in feedback control of power applied to an ultrasonic transducer to regulate temperature based on impedance is given by the expression:
  • the prior probability distribution 133042 includes a state variance defined by the expression:
  • the state variance (3 ⁇ 4 ) is used to predict the next state of the system, which is represented as the prediction (state) probability distribution 133044.
  • the observation probability distribution 133046 is the probability distribution of the actual observation of the state of the system where the observation variance a m is used to define the gain, which is given by the following expression:
  • the initial proof of concept assumed a static, linear relationship between the natural frequency of the electromechanical ultrasonic system and the temperature of the ultrasonic blade.
  • the temperature of the ultrasonic blade tip could be controlled directly.
  • the temperature of the distal tip of the ultrasonic blade can be controlled to not exceed the melting point of the Teflon pad.
  • FIG. 46A is a graphical representation 133050 of temperature versus time of an ultrasonic device without temperature feedback control. Temperature (°C) of the ultrasonic blade is shown along the vertical axis and time (sec) is shown along the horizontal axis. The test was conducted with a chamois located in the jaws of the ultrasonic device. One jaw is the ultrasonic blade and the other jaw is the clamp arm with a TEFLON pad. The ultrasonic blade was excited at the resonant frequency while in frictional engagement with the chamois clamped between the ultrasonic blade and the clamp arm. Over time, the temperature (°C) of the ultrasonic blade increases due to the frictional engagement with the chamois.
  • the temperature profile 133052 of the ultrasonic blade increases until the chamois sample is cut after about 19.5 seconds at a temperature of 220°C as indicated at point 133054.
  • the temperature of the ultrasonic blade increases to a temperature well above the melting point of TEFLON ⁇ 380°C up to ⁇ 490°C.
  • the temperature of the ultrasonic blade reaches a maximum temperature of 490°C until the TEFLON pad is completely melted.
  • the temperature of the ultrasonic blade drops slightly from the peak temperature at point 133056 after the pad is completely gone.
  • 46B is a plot of temperature versus time of an ultrasonic device with temperature feedback control, in accordance with at least one aspect of the present disclosure. Temperature (°C) of the ultrasonic blade is shown along the vertical axis and the time (sec) is shown along the horizontal axis. The test was conducted with a chamois sample located in the jaws of the ultrasonic device. One jaw is the ultrasonic blade and the other jaw is the clamp arm with a TEFLON pad. The ultrasonic blade was excited at the resonant frequency while in frictional engagement with the chamois clamped between the ultrasonic blade and the clamp arm pad.
  • the temperature profile 133062 of the ultrasonic blade increases until the chamois sample is cut after about 23 seconds at a temperature of 220°C as indicated at point 133064.
  • the temperature of the ultrasonic blade increases up to a maximum temperature of about 380°C, just below the melting point of TEFLON, as indicated at point 133066 and then is lowered to an average of about 330°C as indicated generally at region 133068, thus preventing the TEFLON pad from melting.
  • the ultrasonic blade When an ultrasonic blade is immersed in a fluid-filled surgical field, the ultrasonic blade cools down during activation rendering less effective for sealing and cutting tissue in contact therewith.
  • the cooling down of the ultrasonic blade may lead to longer activation times and/or hemostasis issues because adequate heat is not delivered to the tissue.
  • more energy delivery may be required to shorten the transection times and achieve suitable hemostasis under these fluid immersion conditions.
  • the output power of the generator can be increased to compensate for cooling due to blood/saline/other fluid present in the surgical field.
  • the frequency-temperature feedback control system described herein can improve the performance of an ultrasonic device especially when the ultrasonic blade is located or immersed, partially or wholly, in a fluid-filled surgical field.
  • the frequency-temperature feedback control system described herein minimizes long activation times and/or potential issues with ultrasonic device performance in fluid-filled surgical field.
  • the temperature of the ultrasonic blade may be inferred by detecting the impedance of the ultrasonic transducer given by the following expression: or equivalently, detecting the phase angle f between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer.
  • the phase angle f information also may be used to infer the conditions of the ultrasonic blade. As discussed with particularity herein, the phase angle f changes as a function of the temperature of the ultrasonic blade. Therefore, the phase angle f information may be employed to control the temperature of the ultrasonic blade.
  • FIGS. 47A-47B are graphical representations of temperature feedback control for adjusting ultrasonic power applied to an ultrasonic transducer when a sudden drop in temperature of an ultrasonic blade is detected.
  • FIG. 47A is a graphical representation of ultrasonic power output 133070 as a function of time, in accordance with at least one aspect of the present disclosure. Power output of the ultrasonic generator is shown along the vertical axis and time (sec) is shown along the horizontal axis.
  • FIG. 47B is a graphical representation of ultrasonic blade temperature 133080 as a function of time, in accordance with at least one aspect of the present disclosure.
  • Ultrasonic blade temperature is shown along the vertical axis and time (sec) is shown along the horizontal axis.
  • the temperature of the ultrasonic blade increases with the application of constant power 133072 as shown in FIG. 47A.
  • the temperature of the ultrasonic blade suddenly drops. This may result from a variety of conditions, however, during use, it may be inferred that the temperature of the ultrasonic blade drops when it is immersed in a fluid-filled surgical field (e.g., blood, saline, water, etc.).
  • a fluid-filled surgical field e.g., blood, saline, water, etc.
  • the frequency-temperature feedback control algorithm detects the drop in temperature and begins to increase or“ramp up” the power as shown by the power ramp 133074 delivered to the ultrasonic blade to start raising the temperature of the ultrasonic blade above the desired minimum temperature 133082.
  • the ultrasonic generator is outputs substantially constant power 133072 as long the temperature of the ultrasonic blade remains above the desired minimum temperature 133082.
  • processor or control circuit in the generator or instrument or both detects the drop in temperature of the ultrasonic blade below the desired minimum temperature 133072 and initiates a frequency-temperature feedback control algorithm to raise the temperature of the ultrasonic blade above the minimum desired temperature 133082.
  • the generator power begins to ramp 133074 at ti corresponding to the detection of a sudden drop in the temperature of the ultrasonic blade at t 0 . Under the frequency- temperature feedback control algorithm, the power continues to ramp 133074 until the temperature of the ultrasonic blade is above the desired minimum temperature 133082.
  • FIG. 48 is a logic flow diagram 133090 of a process depicting a control program or a logic configuration to control the temperature of an ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • the processor or control circuit of the generator or instrument or both executes one aspect of a frequency-temperature feedback control algorithm discussed in connection with FIGS. 47A and 47B to apply 133092 a power level to the ultrasonic transducer to achieve a desired temperature at the ultrasonic blade.
  • the generator monitors 133094 the phase angle f between the voltage V g (t) and current lg(t) signals applied to drive the ultrasonic transducer.
  • the generator infers 133096 the temperature of the ultrasonic blade using the techniques described herein in connection with FIGS. 43A-45.
  • the generator determines 133098 whether the temperature of the ultrasonic blade is below a desired minimum temperature by comparing the inferred temperature of the ultrasonic blade to a predetermined desired temperature.
  • the generator then adjusts the power level applied to the ultrasonic transducer based on the comparison. For example, the process continues along NO branch when the temperature of the ultrasonic blade is at or above the desired minimum temperature and continues along YES branch when the temperature of the ultrasonic blade is below the desired minimum temperature.
  • the generator increases 133100 the power level to the ultrasonic transducer, e.g., by increasing the voltage V g (t) and/or current l g (t) signals, to raise the temperature of the ultrasonic blade and continues increasing the power level applied to the ultrasonic transducer until the temperature of the ultrasonic blade increases above the minimum desired temperature.
  • FIG. 49 is a graphical representation 1331 10 of ultrasonic blade temperature as a function of time during a vessel firing, in accordance with at least one aspect of the present disclosure.
  • a plot 1331 12 of ultrasonic blade temperature is graphed along the vertical axis as a function of time along the horizontal axis.
  • the frequency-temperature feedback control algorithm combines the temperature of the ultrasonic blade feedback control with the jaw sensing ability.
  • the frequency-temperature feedback control algorithm provides optimal hemostasis balanced with device durability and can deliver energy intelligently for best sealing while protecting the clamp arm pad.
  • the optimum temperature 1331 14 for vessel sealing is marked as a first target temperature T 1 and the optimum temperature 1331 16 for“infinite” clamp arm pad life is marked as a second target temperature T 2 .
  • the frequency-temperature feedback control algorithm infers the temperature of the ultrasonic blade and maintains the temperature of the ultrasonic blade between the first and second target temperature thresholds Ti and T 2 .
  • the generator power output is thus driven to achieve optimal ultrasonic blade temperatures for sealing vessels and prolonging the life of the clamp arm pad.
  • the temperature of the ultrasonic blade increases as the blade heats up and eventually exceeds the first target temperature threshold Ti.
  • the frequency-temperature feedback control algorithm takes over to control the temperature of the blade to Ti until the vessel transection is completed 1331 18 at to and the ultrasonic blade temperature drops below the second target temperature threshold T 2 .
  • a processor or control circuit of the generator or instrument or both detects when the ultrasonic blade contacts the clamp arm pad.
  • the frequency-temperature feedback control algorithm switches to controlling the temperature of the ultrasonic blade to the second target threshold T 2 to prolong the life of the clam arm pad.
  • the optimal clamp arm pad life temperature for a TEFLON clamp arm pad is approximately 325°C.
  • the advanced tissue treatment can be announced to the user at a second activation tone.
  • FIG. 50 is a logic flow diagram 133120 of a process depicting a control program or a logic configuration to control the temperature of an ultrasonic blade between two temperature set points as depicted in FIG. 49, in accordance with at least one aspect of the present disclosure.
  • the generator executes one aspect of the frequency- temperature feedback control algorithm to apply 133122 a first power level to the ultrasonic transducer, e.g., by adjusting the voltage V g (t) and/or the current l g (t) signals applied to the ultrasonic transducer, to set the ultrasonic blade temperature to a first target Ti optimized for vessel sealing.
  • the generator monitors 133124 the phase angle f between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer and based on the phase angle f, the generator infers 133126 the temperature of the ultrasonic blade using the techniques described herein in connection with FIGS. 43A-45.
  • a processor or control circuit of the generator or instrument or both maintains the ultrasonic blade temperature at the first target temperature Ti until the transection is completed.
  • the frequency-temperature feedback control algorithm may be employed to detect the completion of the vessel transection process.
  • the processor or control circuit of the generator or instrument or both determines 133128 when the vessel transection is complete. The process continues along NO branch when the vessel transection is not complete and continues along YES branch when the vessel transection is complete.
  • the processor or control circuit of the generator or instrument or both determines 133130 if the temperature of the ultrasonic blade is set at temperature T ⁇ optimized for vessel sealing and transecting. If the ultrasonic blade temperature is set at Ti , the process continues along the YES branch and the processor or control circuit of the generator or instrument or both continues to monitor 133124 the phase angle f between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer and based on the phase angle f. If the ultrasonic blade temperature is not set at Ti , the process continues along NO branch and the processor or control circuit of the generator or instrument or both continues to apply 133122 a first power level to the ultrasonic transducer.
  • the processor or control circuit of the generator or instrument or both applies 133132 a second power level to the ultrasonic transducer to set the ultrasonic blade to a second target temperature T 2 optimized for preserving or extending the life of the clamp arm pad.
  • the processor or control circuit of the generator or instrument or both determines 133134 if the temperature of the ultrasonic blade is at set temperature T 2 . If the temperature of the ultrasonic blade is set at T2, the process completes 133136 the vessel transection procedure.
  • Knowing the temperature of the ultrasonic blade at the beginning of a transection can enable the generator to deliver the proper quantity of power to heat up the blade for a quick cut or if the blade is already hot add only as much power as would be needed. This technique can achieve more consistent transection times and extend the life of the clam arm pad (e.g., a TEFLON clamp arm pad). Knowing the temperature of the ultrasonic blade at the beginning of the transection can enable the generator to deliver the right amount of power to the ultrasonic transducer to generate a desired amount of displacement of the ultrasonic blade.
  • the clam arm pad e.g., a TEFLON clamp arm pad
  • FIG. 51 is a logic flow diagram 133140 of a process depicting a control program or a logic configuration to determine the initial temperature of an ultrasonic blade, in accordance with at least one aspect of the present disclosure.
  • the resonant frequencies of ultrasonic blades are measured at room temperature or at a predetermined ambient temperature.
  • the baseline frequency values are recorded and stored in a lookup table of the generator or instrument or both. The baseline values are used to generate a transfer function.
  • the generator measures 133142 the resonant frequency of the ultrasonic blade and compares 133144 the measured resonant frequency to the baseline resonant frequency value and determines the difference in frequency ( D .
  • the Af is compared to the lookup table or transfer function for corrected ultrasonic blade temperature.
  • the resonant frequency of the ultrasonic blade may be determined by sweeping the frequency of the voltage Vg(t) and current l g (t) signals applied to the ultrasonic transducer.
  • the resonant frequency is that frequency at which the phase angle f voltage V g (t) and current l g (t) signals is zero as described herein.
  • the processor or control circuit of the generator or instrument or both determines 133146 the initial temperature of the ultrasonic blade based on the difference between the measured resonant frequency and the baseline resonant frequency.
  • the generator sets the power level delivered the ultrasonic transducer, e.g., by adjusting the voltage V g (t) or current l g (t) drive signals or both, to one of the following values prior to activating the ultrasonic transducer.
  • the processor or control circuit of the generator or instrument or both determines 133148 if the initial temperature of the ultrasonic blade is low. If the initial temperature of the ultrasonic blade is low, the process continues along YES branch and the processor or control circuit of the generator or instrument or both applies 133152 a high power level to the ultrasonic transducer to increase the temperature of the ultrasonic blade and completes 133156 the vessel transection procedure.
  • the process continues along NO branch and the processor or control circuit of the generator or instrument or both determines 133150 if the initial temperature of the ultrasonic blade is high. If the initial temperature of the ultrasonic blade is high, the process proceeds along YES branch and the processor or control circuit of the generator or instrument or both applies 133154 a low power level to the ultrasonic transducer to decrease the temperature of the ultrasonic blade and completes 133156 the vessel transection procedure. If the initial temperature of the ultrasonic blade is not high, the process continues along NO branch and the processor or control circuit of the generator or instrument or both completes 133156 the vessel transection.
  • the temperature of an ultrasonic blade and the contents within the jaws of an ultrasonic end effector can be determined using the frequency-temperature feedback control algorithms described herein.
  • the frequency/temperature relationship of the ultrasonic blade is employed to control ultrasonic blade instability with temperature.
  • FIG. 52 is a logic flow diagram 133160 of a process depicting a control program or a logic configuration to determine when an ultrasonic blade is approaching instability and then adjusting the power to the ultrasonic transducer to prevent instability of the ultrasonic transducer, in accordance with at least one aspect of the present disclosure.
  • frequency/temperature relationship of an ultrasonic blade that exhibits a displacement or modal instability is mapped by sweeping the frequency of the drive voltage V g (t) or current l g (t) signals, or both, over the temperature of the ultrasonic blade and recording the results.
  • a function or relationship is developed that can be used/interpreted by a control algorithm executed by the generator. Trigger points can be established using the relationship to notify the generator that an ultrasonic blade is approaching the known blade instability.
  • the generator executes a frequency-temperature feedback control algorithm processing function and closed loop response such that the driving power level is reduced (e.g., by lowering the driving voltage V g (t) or current l g (t), or both, applied to the ultrasonic transducer) to modulate the temperature of the ultrasonic blade at or below the trigger point to prevent a given blade from reaching instability.
  • Advantages include simplification of ultrasonic blade configurations such that the instability characteristics of the ultrasonic blade do not need to be designed out and can be compensated using the present instability control technique.
  • the present instability control technique also enables new ultrasonic blade geometries and can improve stress profile in heated ultrasonic blades. Additionally, ultrasonic blades can be configured to diminish performance of the ultrasonic blade if used with generators that do not employ this technique.
  • the processor or control circuit of the generator or instrument or both monitors 133162 the phase angle f between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer.
  • the processor or control circuit of the generator or instrument or both infers 133164 the temperature of the ultrasonic blade based on the phase angle f between the voltage V g (t) and current l g (t) signals applied to the ultrasonic transducer.
  • the processor or control circuit of the generator or instrument or both compares 133166 the inferred temperature of the ultrasonic blade to an ultrasonic blade instability trigger point threshold.
  • the processor or control circuit of the generator or instrument or both determines 133168 whether the ultrasonic blade is approaching instability. If not, the process proceed along the NO branch and monitors 133162 the phase angle f, infers 133164 the temperature of the ultrasonic blade, and compares 133166 the inferred temperature of the ultrasonic blade to an ultrasonic blade instability trigger point threshold until the ultrasonic blade approaches instability. The process then proceeds along the YES branch and the processor or control circuit of the generator or instrument or both adjusts 133170 the power level applied to the ultrasonic transducer to modulate the temperature of the ultrasonic blade.
  • Ultrasonic sealing algorithms for ultrasonic blade temperature control can be employed to improve hemostasis utilizing a frequency-temperature feedback control algorithm described herein to exploit the frequency/temperature relationship of ultrasonic blades.
  • a frequency-temperature feedback control algorithm may be employed to alter the power level applied to the ultrasonic transducer based on measured resonant frequency (using spectroscopy) which relates to temperature, as described in various aspects of the present disclosure.
  • the frequency-temperature feedback control algorithm may be activated by an energy button on the ultrasonic instrument.
  • a frequency-temperature feedback control algorithm sets a limit on the temperature threshold that the tissue can reach as the tissue heats up during the higher power level stage and then reduces the power level to control the temperature of the ultrasonic blade based on the melting point of the clamp jaw pad (e.g., TEFLON) to complete the seal.
  • the control algorithm can be implemented by activating an energy button on the instrument for a more responsive/adaptive sealing to reduce more the complexity of the hemostasis algorithm.
  • FIG. 53 is a logic flow diagram 133180 of a process depicting a control program or a logic configuration to provide ultrasonic sealing with temperature control, in accordance with at least one aspect of the present disclosure.
  • the processor or control circuit of the generator or instrument or both activates 133182 ultrasonic blade sensing using spectroscopy (e.g., smart blade) and measures 133184 the resonant frequency of the ultrasonic blade (e.g., the resonant frequency of the ultrasonic electromechanical system) to determine the temperature of the ultrasonic blade using a frequency-temperature feedback control algorithm (spectroscopy) as described herein.
  • spectroscopy e.g., smart blade
  • spectroscopy e.g., the resonant frequency of the ultrasonic electromechanical system
  • the resonant frequency of the ultrasonic electromechanical system is mapped to obtain the temperature of the ultrasonic blade as a function of resonant frequency of the electromechanical ultrasonic system.
  • a first desired resonant frequency f x of the ultrasonic electromechanical system corresponds to a first desired temperature Z° of the ultrasonic blade.
  • the first desired ultrasonic blade temperature Z° is an optimal temperature (e.g., 450°C) for tissue coagulation.
  • a second desired frequency fy of the ultrasonic electromechanical system corresponds to a second desired temperature ZZ° of the ultrasonic blade.
  • the second desired ultrasonic blade temperature ZZ° is a temperature of 330°C, which is below the melting point of the clamp arm pad, which is approximately 380°C for TEFLON.
  • the processor or control circuit of the generator or instrument or both compares 133186 the measured resonant frequency of the ultrasonic electromechanical system to the first desired frequency f x . In other words, the process determines whether the temperature of the ultrasonic blade is less than the temperature for optimal tissue coagulation. If the measured resonant frequency of the ultrasonic electromechanical system is less than the first desired frequency f x , the process continues along the NO branch and the processor or control circuit of the generator or instrument or both increases 133188 the power level applied to the ultrasonic transducer to increase the temperature of the ultrasonic blade until the measured resonant frequency of the ultrasonic electromechanical system exceeds the first desired frequency f x . In which case, the tissue coagulation process is completed and the process controls the temperature of the ultrasonic blade to the second desired temperature corresponding to the second desired frequency f y .
  • the process continues along the YES branch and the processor or control circuit of the generator or instrument or both decreases 133190 the power level applied to the ultrasonic transducer to decrease the temperature of the ultrasonic blade.
  • the processor or control circuit of the generator or instrument or both measures 133192 the resonant frequency of the ultrasonic electromechanical system and compares the measured resonant frequency to the second desired frequency f Y . If the measured resonant frequency is not less than the second desired frequency f Y , the processor or control circuit of the generator or instrument or both decreases 133190 the ultrasonic power level until the measured resonant frequency is less than the second desired frequency f Y .
  • the frequency-temperature feedback control algorithm to maintain the measured resonant frequency of the ultrasonic electromechanical system below the second desired frequency f y , e.g., the temperature of the ultrasonic blade is less than the temperature of the melting point of the clamp arm pad then, the generator executes the increases the power level applied to the ultrasonic transducer to increase the temperature of the ultrasonic blade until the tissue transection process is complete 133196.
  • FIG. 54 is a graphical representation 133200 of ultrasonic transducer current and ultrasonic blade temperature as a function of time, in accordance with at least one aspect of the present disclosure.
  • FIG. 54 illustrates the results of the application of the frequency-temperature feedback control algorithm described in FIG. 53.
  • the graphical representation 133200 depicts a first plot 133202 of ultrasonic blade temperature as a function of time with respect to a second plot 133204 of ultrasonic transducer current l g (t) as a function of time. As shown, the transducer lg(t) is maintained constant until the ultrasonic blade temperature reaches 450°, which is an optimal coagulation temperature.
  • the frequency-temperature feedback control algorithm decrease the transducer current l g (t) until the temperature of the ultrasonic blade drops to below 330°, which is below the melting point of a TEFLON pad, for example.
  • a surgical instrument e.g., an ultrasonic surgical instrument
  • a surgical instrument is configured to identify or parameterize the tissue grasped by the end effector and adjust various operational parameters of the surgical instrument accordingly. The identification or
  • the ultrasonic surgical instrument is configured to tune the displacement amplitude of the distal tip of the ultrasonic blade according to the collagen/elastin ratio of the tissue detected in the jaws of the end effector.
  • an ultrasonic instrument comprises an ultrasonic transducer acoustically coupled to an ultrasonic blade via an ultrasonic waveguide.
  • the displacement of the ultrasonic blade is a function of the electrical power applied to the ultrasonic transducer and, accordingly, the electrical power supplied to the ultrasonic transducer can be modulated according to the detected collagen/elastin ratio of the tissue.
  • the force exerted by the clamp arm on the tissue can be modulated according to the location of the tissue relative to the end effector.
  • FIG. 55 is a bottom view of an ultrasonic end effector 1 122 showing a clamp arm 1 140 and ultrasonic blade 1 128 and delineating tissue positioning within the ultrasonic end effector 1 122, in accordance with at least one aspect of the present disclosure.
  • the positioning of the tissue between the clamp arm 1 140 and ultrasonic blade 1 128 can be delineated according to the region or zone in which the tissue is located, such as a distal region 130420 and a proximal region 130422.
  • the ultrasonic end effector 1 122 grasps tissue between the ultrasonic blade 1 128 and clamp arm 1 140.
  • the ultrasonic generator e.g., the generator 1 100 described in connection with FIG. 22
  • the power applied to the ultrasonic transducer may be in a therapeutic or non-therapeutic range of energy levels.
  • the resulting displacement of the ultrasonic blade 1 128 does not effect, or minimally effects, the grasped tissue so as not to coagulate or cut the tissue.
  • the non-therapeutic excitation may be particularly useful for determining the impedance of the ultrasonic transducer, which will vary based on a variety of conditions present at the end effector 1 122, including, for example, tissue type, tissue location within the end effector, ratio of different tissue types, and temperature of the ultrasonic blade, among other conditions. A variety of these conditions are described herein.
  • the impedance of the ultrasonic transducer is given by as described herein.
  • therapeutic ultrasonic energy may be applied based on the determined end effector 1 122 conditions to optimize the tissue treatment, effective seal, transection, and duration, among other variables associated with a particular surgical procedure. Therapeutic energy is sufficient to coagulate and cut tissue.
  • the present disclosure provides a control process, such as an algorithm, to determine the thickness and type of tissue located within the jaws (i.e., between the clamp arm 1 140 and the ultrasonic blade 1 128) of an ultrasonic end effector 1 122 as shown in FIGS.
  • a control process such as an algorithm
  • FIG. 56 is a graphical representation 130000 depicting change in ultrasonic transducer impedance as a function tissue location within the ultrasonic end effector 1 122 over a range of predetermined ultrasonic generator power level increases, in accordance with at least one aspect of the present disclosure.
  • the horizontal axis 130004 represents tissue location and the vertical axis 130002 represents transducer impedance (W).
  • Various limits along the horizontal axis 130004 such as a first or proximal limit 130010 and a second or distal limit 130012, can delineate or correspond to different positions of the tissue grasped within the ultrasonic end effector 1 122. The delineation of proximal and distal tissue locations is shown schematically in FIG.
  • the plots 130006, 130008 represent the change in transducer impedance W as the power applied to the ultrasonic transducer is varied from a minimum or first non-therapeutic power level to a maximum or second non-therapeutic power level l_ 2 .
  • di represents the change in transducer impedance when tissue is located at the proximal portion 130422 of the end effector 1 122. This can be seen from the fact that the first plot 130006 does not exceed the proximal limit 130010.
  • d 2 represents the change in transducer impedance when tissue is located at the distal end 130012 of the end effector 1 122. This can be seen from the fact that the first plot 130006 exceeds the proximal limit 130010 and/or is located near to the distal limit 130012. As indicated by the plots 130006, 130008, d 2 is much greater than di .
  • the resulting measured transducer impedance (W) is a useful indicator of the position of tissue within the jaw of the end effector 1 122, whether at the distal end 130420 or proximal end 130422 of the ultrasonic blade 1 128 as shown in FIG. 55.
  • the location of the tissue within the end effector 1 122 can be determined based on the change in transducer impedance d as the non-therapeutic power level applied to the ultrasonic transducer is varied from a minimum power level (e.g., I_i) to a maximum power level (e.g., I_ 2 ).
  • the non-therapeutic power level(s) applied to the ultrasonic transducer can cause the ultrasonic blade 1 128 to oscillate at a sensing amplitude or below the minimum therapeutic amplitude (e.g., less than or equal to 35 pm at the distal and/or proximal end of the ultrasonic blade 1 128). Calculation of impedance is discussed previously in this disclosure.
  • a measure of the first transducer impedance Zi is taken when a first power level is applied, which provides an initial measurement, and a subsequent measure of impedance Z 2 is taken again when the applied power is increased to a second power level l_ 2 .
  • the resulting longitudinal displacement amplitude of the ultrasonic blade 1 128, based on the applied power level provides an indication of tissue location within the jaws of the end effector 1 122.
  • the first power level produces a longitudinal displacement amplitude of 35 pm at the distal end 130420 and 15 pm at the proximal end 130422.
  • the second power level l_ 2 produces a
  • An algorithm calculates the difference in transducer impedance d between the first and second measurements to find the change in impedance AZ g (t).
  • the change in impedance d is plotted against tissue location and shows that a higher change in impedance represents tissue location distributed at the distal end 130012 and a lower change in impedance represents tissue location distributed at the proximal end 130010 of the end effector 1 122.
  • FIG. 57 is a graphical representation 130050 depicting change in ultrasonic transducer impedance as a function of time relative to the location of tissue within the ultrasonic end effector, in accordance with at least one aspect of the present disclosure.
  • the horizontal axis 130054 represents time (t) and the vertical axis 130052 represents change in transducer impedance (d) between the first and second measurements.
  • the plots 130060, 130066 depict the change in transducer impedance (d) versus time (t), relative to the proximal and distal location of tissue within the bite of the clamp arm 1 140.
  • a clamp arm 1 140 force is applied to hold the tissue in the ultrasonic end effector 1 122 and a delay period is applied before a first, low-power level is applied and the transducer impedance is measured. Subsequently, the system applies a second, higher power level and measures the impedance again. It will be appreciated that both the first and second power levels applied to the ultrasonic transducer are non-therapeutic power levels.
  • the 18 calculates the difference in transducer impedance (d) between the first power level and the second power level for the proximal and distal tissue locations. As shown in relation to the first plot 130060, if the difference in transducer impedance (d) below a first threshold 130056, the algorithm determines that the tissue is located in the proximal portion 130422 of the end effector 1 122. In the first plot 130060, the difference in the transducer impedance between the measurements increases 130062 over time until it plateaus or maintains 130064 below the first threshold 130056.
  • the algorithm determines that the tissue is located in the distal portion 130420 of the of the end effector 1 122.
  • the difference in the transducer impedance between the measurements increases 130068 over time until it plateaus or maintains 130070 above the second threshold 130058.
  • the algorithm determines that the tissue is located in the middle portion 130424 of the end effector 1 122, e.g., between the proximal and distal portions of the end effector.
  • FIG. 58 is a logic flow diagram of a process 130100 depicting a control program or a logic configuration to identify operation in the non-therapeutic range of power applied to the instrument in order to determine tissue positioning, in accordance with at least one aspect of the present disclosure.
  • the process 130100 can be executed by a processor or control circuit of a surgical instrument, such as the control circuit 760 of FIG. 18, or a generator, such as the processor 902 of FIG. 21 .
  • the process 130100 will be described as being executed by a processor, but it should be understood that the following description
  • a processor applies a control signal to close the clamp arm 1 140 to capture the tissue between the clamp arm 1 140 and the ultrasonic blade 1 128. After the clamp arm 1 140 closes onto the tissue, the processor waits for a predetermined delay period to allow the tissue to relax and give up some moisture content. After the delay period, the processor sets 130102 the power level applied to ultrasonic transducer to a first non-therapeutic power level.
  • one aspect of the process 130100 includes a feedback control can be used to verify that the first power is set below a therapeutic power level. In this aspect, the processor determines 130106 whether the first power level is less than a therapeutic power level.
  • the process 130100 continues along the NO branch and the processor decreases 130108 the applied power and loops until the first power level is less than a therapeutic power level.
  • the process 130100 then continues along the YES branch and the processor measures 1301 10 a first impedance Z gi (t) of the ultrasonic transducer corresponding to the first power level.
  • the processor sets 1301 12 the power level applied to ultrasonic transducer to a second non- therapeutic power level, where the second power is greater than the first power level and is below a therapeutic power level.
  • a feedback control can be used to verify that the second power level is not only greater than the first power level but also is below a therapeutic power level.
  • the processor determines 1301 14 whether the second power level is less than a therapeutic power level. If the second power is greater than a therapeutic power level, the process 130100 continues along the NO branch and the processor decreases 130108 the second power level and loops until it is below a therapeutic power level threshold. The process 130100 then continues along the YES branch and the processor measures 1301 16 a second impedance Z g2 (t) of the ultrasonic transducer corresponding to the second power level. The impedance of the ultrasonic transducer can be measured using a variety of techniques as discussed herein. The processor then calculates 1301 18 the difference in transducer impedance between the applied first and second power levels:
  • the processor then provides 130120 an indication of the tissue position to the user.
  • the processor can indicate the tissue position via an output device of a surgical instrument (e.g., visual feedback devices, such as the display depicted in FIG. 31 , audio feedback devices, and/or tactile feedback devices), a display 135 (FIG. 3), or other output device of a surgical hub 106 communicably connected to the surgical instrument and/or an output device 2140 (FIG. 27B) of a generator 1 100 (e.g., visual feedback devices, audio feedback devices, and/or tactile feedback devices).
  • a surgical instrument e.g., visual feedback devices, such as the display depicted in FIG. 31 , audio feedback devices, and/or tactile feedback devices
  • a display 135 FIG. 3
  • other output device of a surgical hub 106 communicably connected to the surgical instrument and/or an output device 2140 (FIG. 27B) of a generator 1 100 (e.g., visual feedback devices, audio feedback devices, and/or tactile feedback devices).
  • the processor compares the difference in transducer impedance to a first and second threshold where, as shown in FIG. 57, if the difference in transducer impedance (d) below a first threshold 130056, the algorithm determines that the tissue is located in the proximal portion 130422 of the end effector 1 122 and if the difference in transducer impedance (d) is above a second threshold 130058, the algorithm determines that the tissue is located in the distal portion 130420 of the of the end effector 1 122.
  • the algorithm determines that the tissue is located in the middle portion 130424 of the end effector 1 122, e.g., between the proximal and distal portions 130422, 130420 of the end effector 1 122.
  • the impedance of the ultrasonic transducer can be employed to differentiate what percent of tissue is located in a distal, proximal, or intermediate location of the end effector 1 122 and then apply a suitable therapeutic power level.
  • the reactions of the ultrasonic instrument may be based on whether tissue is present within the end effector, the type of tissue located in the end effector, or the compressibility or composition of the tissue located in the end effector.
  • the generator or the ultrasonic surgical instrument may contain and/or execute instructions to perform algorithms to control the time between clamping the tissue in the jaws of the end effector and the activation of the ultrasonic transducer to treat the tissue. If tissue is not sensed, the ultrasonic generator activation buttons or pedals may be assigned different meanings to execute different functions.
  • an advanced energy device may employ the detection of the presence of tissue within the jaws of the end effector as the queue for activating the ultrasonic transducer, thereby starting the tissue coagulation cycle.
  • the compressive properties and situational awareness may enable automatic activation of the device to also adjust the parameters of the algorithm for the type of tissue sensed. For example, the advanced generator may ignore activations of buttons or foot pedals unless tissue is sensed in contact with the jaws of the end effector. This configuration would eliminate inadvertent activation queues that would allow the device to be operated in a simpler manner.
  • an advanced generator such as advanced generators described in connection with FIGS. 1-42, and/or surgical instruments, such as ultrasonic surgical instruments described throughout this disclosure, may be configured to operate in a switchless mode.
  • the ultrasonic device In a switchless mode, the ultrasonic device is automatically activated in coagulation mode upon sensing or detecting the presence of tissue in the jaws of the end effector.
  • control algorithm controlling the activation of the ultrasonic surgical instrument can be configured to apply less energy initially to the ultrasonic instrument than if activated when not operating in the switchless mode.
  • the ultrasonic generator or instrument can be configured to determine both contact with and the type of tissue located in the jaws of the end effector. Based on sensing or detecting the presence of tissue in the jaws of the end effector, control algorithms executed either by a processor or control circuit of the generator or ultrasonic instrument could run the ultrasonic instrument in switchless mode and could adjust the algorithm to achieve the best overall coagulation of the tissue in the jaws of the end effector. In other aspects, in lieu of automatically activating the surgical instrument and/or generator, control algorithms executed by a processor or control circuit of the generator or ultrasonic instrument could prevent activation of the generator or ultrasonic instrument unless the presence of tissue is detected within the end effector.
  • the present disclosure provides an algorithm executed by a processor or control circuit located either in the generator or handheld ultrasonic instrument to determine the presence of tissue and the type of tissue located within the jaws of the end effector.
  • the control algorithm can be configured to determine that tissue is located within the end effector via techniques described herein for determining tissue location as described below under the heading DETERMINING TISSUE LOCATION VIA ELECTRODE CONTINUITY.
  • a control algorithm can be configured to determine whether tissue is located within the end effector according to whether there is any continuity between electrodes (as described below) and, accordingly, activate the surgical instrument (e.g., by causing the generator to which the surgical instrument is coupled to begin applying power to the surgical instrument) automatically upon detecting tissue or permit activation of the surgical instrument.
  • the control algorithm can further be configured to activate the surgical instrument at a particular power level, which may or may not be different that a standard initial activation power level for the surgical instrument.
  • a control algorithm can be configured to activate or permit activation of the surgical instrument according to the particular type or composition of the tissue, which can be detected via, e.g., techniques described below under the heading DETERMINING TISSUE COLLAGEN-TO-ELASTIN RATIO ACCORDING TO IR SURFACE REFLECTANCE AND EMISSIVITY.
  • the control algorithm can be configured to activate the surgical instrument when tissue having a high collagen composition has been grasped, but not necessarily activate the surgical instrument when tissue having a high elastin composition has been grasped.
  • a control algorithm can be configured to activate or permit activation of the surgical instrument according to whether the grasped tissue is located at a particular position within the end effector or whether a particular amount of tissue has been grasped by the end effector via, e.g., techniques described below under the heading DETERMINING TISSUE LOCATION VIA ELECTRODE CONTINUITY.
  • the control algorithm can be configured to activate the surgical instrument when the grasped tissue covers a particular percentage of the end effector.
  • the control algorithm can be configured to activate the surgical instrument when the grasped tissue is located at the distal end of the end effector.
  • a control algorithm can be configured to determine whether tissue has been grasped by the end effector, the tissue type or composition, and other characteristics of the end effector or the tissue via a situational awareness system, as described in U.S.
  • a surgical hub 106 (FIGS. 1-1 1) to which the surgical instrument and/or generator is connected can receive data from the surgical instrument, generator, and/or other medical devices utilized in the operating theater and make inferences about the surgical procedure, or a particular step thereof, being performed. Accordingly, the situational awareness system can infer whether and what type(s) of tissue are being operated on at any given instant or step and then a control algorithm can control the surgical instrument accordingly, including automatically activating the surgical instrument accordingly.
  • the control algorithm could be configured to automatically activate or permit activation of the surgical instrument when the tissue grasped by the end effector corresponds to the tissue type or tissue composition expected by the situational awareness system.
  • the ultrasonic instrument With the ability to detect whether or not the instrument is contacting tissue, and what type of tissue when in contact, the ultrasonic instrument can be operated in a switchless mode of operation where operation is permitted based on the sensing ability of the ultrasonic instrument.
  • a control algorithm can be configured to ignore actuations of activation buttons, foot pedals, and other input devices coupled to the generator and/or the ultrasonic surgical instrument unless tissue is sensed in contact with the jaws/end effector of the surgical instrument, thereby preventing unintended activations of the instrument.
  • a control algorithm can be configured to assign different meanings to the inputs of activation buttons, foot pedals, and other input devices coupled to the generator and/or the ultrasonic surgical instrument according to whether tissue is sensed in contact with the jaws/end effector of the surgical instrument. For example, when tissue is present in the end effector, a control algorithm can be configured to activate the surgical instrument in response to an activation button being actuated; however, when tissue is not present within the end effector, the control algorithm can be configured to execute some different or secondary action when the activation button is actuated.
  • the ability to determine the lack of tissue present in the jaws of the end effector acts as a permissive to allow the instrument to change to switchless mode and then initiate an automatic coagulation cycle of operation when tissue is then detected, leading to greater uptime use of the instrument and allowing the user to proceed based on its predictive capability.
  • the ability to further detect tissue type in addition to detecting the presence of tissue allows the algorithm to adjust and calculate the best coagulation opportunity.
  • an ultrasonic surgical instrument can include a processor or control circuit executing an adaptive ultrasonic blade control algorithm for detecting the composition of the tissue grasped by or at the end effector and controlling operational parameters of the ultrasonic transducer and/or ultrasonic blade accordingly.
  • the tissue composition can include, for example, the ratio of collagen to elastin in the tissue, the stiffness of the tissue, or the thickness of the tissue.
  • the operational parameters controlled or regulated by the adaptive ultrasonic blade control algorithm can include, for example, the amplitude of the ultrasonic blade, the temperature or heat flux of the ultrasonic blade, and so on.
  • the adaptive ultrasonic blade control algorithm can be executed by a control circuit or processor located either in the generator or the surgical instrument.
  • the adaptive ultrasonic blade control algorithm can be configured to control the amplitude of the ultrasonic blade according to the collagen-to-elastin ratio of the tissue.
  • the collagen-to-elastin ratio of the tissue can be determined via a variety of techniques, such as those described below.
  • the adaptive ultrasonic blade control algorithm can be configured to control the ultrasonic transducer/ultrasonic blade to provide a longer warming time and a lower end temperature of the ultrasonic blade the lower the collagen content of the tissue is.
  • a control algorithm can be configured to determine the collagen-to- elastin ratio of a tissue (e.g., to tune the amplitude of the distal tip of an ultrasonic blade) by detecting the natural frequency of an ultrasonic blade and the shifts in the ultrasonic blade waveform.
  • the techniques described in connection with FIGS. 1-54 may be employed to detect the ratio of collagen to elastin of the tissue located in an end effector of an ultrasonic instrument.
  • the present disclosure provides an adaptive ultrasonic blade control algorithm to detect the natural frequency of the ultrasonic blade and shift in waveform to detect the composition of the tissue in contact with the ultrasonic blade.
  • the adaptive ultrasonic blade control algorithm may be configured to detect the collagen and elastin composition content of the tissue and adjust the therapeutic heat flux of the ultrasonic blade based on the detected collagen content of the tissue.
  • Techniques for monitoring the deviation of the natural frequency of the ultrasonic blade based on the tissue type located in the jaws of the end effector of the ultrasonic instrument are described herein in connection with FIGS. 1-54. Accordingly for conciseness and clarity of disclosure, such techniques will not be repeated here.
  • the ratio of elastin to collagen may be determined by monitoring the shift in the natural frequency of the ultrasonic blade and comparing the natural frequency to a look-up table.
  • the look-up table can be stored in memory (e.g., memory 3326 of FIG. 31 ) and contains the ratio of elastin to collagen and a corresponding natural frequency shift for a particular ratio as determined empirically.
  • a control algorithm can be configured to determine the collagen-to- elastin ratio of a tissue (e.g., to tune the amplitude of the distal tip of an ultrasonic blade) by determining the IR reflectivity of the tissue.
  • FIG. 59 illustrates an ultrasonic system 130164 comprising an ultrasonic generator 130152 coupled to an ultrasonic instrument 130150.
  • the ultrasonic instrument 130150 is coupled to an ultrasonic end effector 130400 via an ultrasonic waveguide 130154.
  • the ultrasonic generator 130152 may be integral with the ultrasonic instrument 130150 or may be connected to the ultrasonic instrument 130150 using wired or wireless electrical/electronic coupling techniques.
  • the end effector 130400 of the ultrasonic surgical instrument 130150 comprises IR sensors located on the clamp arm 130402 (e.g., jaw member), in accordance with at least one aspect of the present disclosure.
  • the ultrasonic generator 130152 and/or the ultrasonic instrument 130150 may be coupled to the surgical hub 130160 and/or the cloud 130162 over wireless or wired connections, as described in connection with FIGS. 1-1 1 .
  • FIG. 60 illustrates an IR reflectivity detection sensor circuit 130409 that may be mounted or formed integrally with the clamp arm 130402 of the ultrasonic end effector 130400 to detect tissue composition, in accordance with at least one aspect of the present disclosure.
  • the IR sensor circuit 130409 includes an IR source 130416 (e.g., and IR transmitter) and IR detector 130418 (e.g., an IR receiver).
  • the IR source 130416 is coupled to a voltage source V.
  • a current is generated through R2 when the control circuit 130420 closes the switch SW1 .
  • the IR source 130416 emits IR energy towards the tissue 130410 (e.g., tissue clamped or situated between the clamp arm 130402 and the ultrasonic blade 130404). Some of the emitted IR energy is absorbed by the tissue 130410, some of the emitted IR energy is transmitted through the tissue 130410, and some of the emitted IR energy is reflected by the tissue 130410.
  • the IR detector 130418 receives the IR energy reflected by tissue 130410 and generates an output voltage V 0 or signal, which is applied to the control circuit 130420 for processing.
  • the ultrasonic generator 130152 includes the control circuit 130420 to drive the IR source 130416 and IR detector 130418 located on or in the clamp arm 130402 of the ultrasonic end effector 130400.
  • the ultrasonic instrument 130150 includes the control circuit 130420 to drive the IR source 130416 and IR detector 130418 located on or in the clamp arm 130402 of the ultrasonic end effector 130400.
  • the IR source 130416 is energized by the control circuit 130420 by closing switch SW1 , for example, to illuminate the tissue with IR energy.
  • the IR detector 130418 generates a voltage V 0 that is proportional to the IR energy reflected by the tissue 130410.
  • the total IR energy emitted by the IR source 130416 equals the sum of the IR energy reflected by the tissue 130410, the IR energy absorbed by the tissue 130410, and the IR energy that passes through the tissue 130410, plus any losses.
  • the control circuit 130420 or processor may be configured to detect the collagen content of the tissue 130410 by the amount of IR energy detected by the IR detector 130418 relative to the total amount of IR energy emitted by the IR source 130416.
  • An algorithm takes into account the amount of energy absorbed by and/or transmitted through the tissue 130410 to determine the collagen content of the tissue 130410.
  • the IR source 130416 and IR detector 130418 and algorithms are calibrated to provide useful measurements of the collagen content of the tissue 130410 using the principles of IR reflectivity.
  • the IR reflectivity detection sensor circuit 130409 shown in FIG. 60 provides IR surface reflectance and emissivity to determine the ratio of elastin to collagen.
  • the IR reflectance may be employed to determine tissue composition for tuning the amplitude of an ultrasonic transducer.
  • the refractive index is an optical constant that controls the light-related reflection of IR light.
  • the refractive index may be employed to differentiate tissue types. For example, the refractive index contrast has been shown to differentiate between normal liver tissue and hepatic metastases. The refractive index could be used as an absolute or a comparative measure for tissue differentiation.
  • a comparative method employs an energy dissection device, such as an ultrasonic blade 130404, for example, to determine the exact ratio (as detailed above) and then to predict the collagen ratio for all further actuation using that index as a baseline.
  • an endoscope may update the dissection device (e.g., ultrasonic blade 130404) based on collagen ratio.
  • the dissection device can fine-tune the forecasting each time it is actuated to make an actual collagen denaturing firing.
  • An alternative method may employ an absolute index with a look-up table that can differentiate between surface irregularities and sub-surface collagen concentration.
  • IR refractive index properties of tissue can be found in Visible To Near-Infrared Refractive Properties Of Freshly-Excised Human-Liver Tissues: Marking Hepatic Malignancies; Panagiotis Giannios, Konstantinos G. Toutouzas, Maria
  • the ultrasonic dissection device can be configured to change the ideal temperature of the ultrasonic blade control algorithm proportionately with the collagen ratio.
  • the ultrasonic blade temperature control algorithm can be modified based on the collagen ratio received from the control circuit 130420.
  • the ultrasonic blade temperature control algorithm can be configured to lower the set of temperatures at which the ultrasonic blade 130404 is maintained and increase the hold time that the ultrasonic blade 130404 is contacted with the tissue 130410 for higher concentrations of collagen in the grasped tissue 130410.
  • the wait time for the algorithm to cycle through a full activation could be modified based on the collagen ratio.
  • Various temperature control algorithms for ultrasonic blades are described in connection with FIGS. 43-54.
  • FIG. 61 is a sectional view of an ultrasonic end effector 130400 comprising a clamp arm 130402 and an ultrasonic blade 130404 according to one aspect of the present disclosure.
  • the clamp arm 130402 comprises IR reflectivity detection sensor circuits 130409a, 130409b that may be mounted or formed integrally with the clamp arm 130402 of the ultrasonic end effector 130400 to detect the composition of the tissue 130410.
  • the IR reflectivity detection sensor circuits 130409a, 130409b may be mounted on a flexible circuit substrate 130412, which is shown in plain view in FIG. 62.
  • the flexible circuit substrate 130412 includes three elongate elements 130408a, 130408b, 130408c on which the IR reflectivity detection sensor circuits 130409a, 130409b and IR sensors 130414a, 130414b are mounted.
  • the IR sensors 130414a, 130414b may include IR sources 130416 and IR detectors 130418 as shown in FIG. 60.
  • FIG. 63 is a logic flow diagram of a process 130200 depicting a control program or a logic configuration to measure IR reflectance to determine tissue composition to tune the amplitude of the ultrasonic transducer.
  • the process 130200 can be executed by a processor or control circuit of a surgical instrument, such as the control circuit 760 of FIG. 18, or a generator, such as the processor 902 of FIG. 21 .
  • a processor or control circuit of a surgical instrument such as the control circuit 760 of FIG. 18, or a generator, such as the processor 902 of FIG. 21 .
  • the process 130200 will be described as being executed by a control circuit, but it should be understood that the following description encompasses the aforementioned variations.
  • the control circuit energizes 130202 the IR source 130416 to apply IR energy to tissue 130410 clamped in an end effector 13400 of an ultrasonic instrument 130150.
  • the control circuit detects 130204, via an IR detector 130418, the IR energy reflected by the tissue 130410.
  • the control circuit determines 130206 the ratio of collagen to elastin of the tissue 130410 based on the detected IR energy reflected by the tissue 130410.
  • the control circuit adjusts 130208 the ultrasonic blade temperature control algorithm, as discussed in U.S. Provisional Patent Application No.
  • the collagen content of the tissue 130410 may be detected by according to the reflectivity of an IR light source 130416.
  • the lower the collagen content of the tissue 130410 the longer the warming time and the lower the end temperature of the ultrasonic blade 130404.
  • the tissue 130410 composition may be tissue thickness or stiffness and could be used to affect the ultrasonic blade transducer control program.
  • the ratio of elastin to collagen may be determined by monitoring the IR reflectance of the tissue and comparing the detected IR reflectance to a look-up table.
  • the look-up table can be stored in memory (e.g., memory 3326 of FIG. 31) and contains the ratio of elastin to collagen and a corresponding IR reflectance for a particular ratio as determined empirically.
  • tissue is composed of varying amounts of structural proteins, such as collagen and elastin, which provide the different types of tissue with different properties.
  • structural proteins such as collagen and elastin
  • the structural proteins denature, which affects the tissue integrity and other tissue properties.
  • the structural proteins denature at different known temperatures. For example, collagen denatures prior to elastin. Accordingly, by detecting at what temperature the properties of the tissue change, one can infer the tissue composition (e.g., the ratio of collagen to elastin in the tissue).
  • a control algorithm can be configured to determine the collagen-to-elastin ratio of a tissue by determining the collagen transformation point of the tissue.
  • the control algorithm can, in turn, control various operational parameters of the surgical instrument, such as the amplitude of the ultrasonic blade, according to the determined tissue composition.
  • the control algorithm can determine the collagen transformation point of the tissue by measuring the position of the clamp arm actuation member and the rate of change of its displacement while maintaining the load on the clamp arm constant.
  • the control algorithm can determine the collagen transformation point of the tissue by measuring the temperature of the tissue/blade interface directly to identify the collagen/elastin percentage.
  • FIGS. 16-19 illustrate schematically motorized clamp arm closure mechanisms.
  • 40 is a system diagram 7400 of a segmented circuit 7401 comprising a plurality of
  • FIG. 35 is a circuit diagram of various components of a surgical instrument with motor control functions, according to one aspect of the present disclosure.
  • FIG. 35 illustrates a drive mechanism 7930, including a closure drivetrain 7934 configured to close a jaw member to grasp tissue with the end effector.
  • FIGS. 38-39 illustrate control systems 12950, 12970 for controlling the rate of closure of the jaw member, such as a clamp arm portion of an ultrasonic end effector, where FIG.
  • FIG. 38 is a diagram of a control system 12950 configured to provide progressive closure of a closure member as it advances distally to close the clamp arm to apply a closure force load at a desired rate according to one aspect of this disclosure
  • FIG. 39 illustrates a proportional-integral- derivative (PID) controller feedback control system 12970 according to one aspect of this disclosure.
  • PID proportional-integral- derivative
  • a control algorithm can be configured to detect the collagen
  • a control algorithm can be configured to control the force applied to the tissue by the clamp arm according to the collagen transformation point. This may be achieved by measuring the position of the clamp arm actuation member and its rate of change while maintaining the load of the clamp arm constant within coaptation pressure within a set operational range (e.g., 130-180 psi) corresponding to the particular instrument type.
  • FIG. 64A is a graphical representation 130250 of the displacement of the clamp arm 1 140 (FIG. 23) versus time as the clamp arm 1 140 is closed to identify the collagen
  • FIG. 64B is a magnified portion 130256 of the graphical representation 130250 shown in FIG. 64A.
  • the horizontal axis 130254 represents time (e.g., in sec.) and the vertical axis 130252 represents clamp arm displacement d (e.g., in mm).
  • a control algorithm can be configured to control the load applied to a tissue by the clamp arm 1 140 (e.g., by controlling the rate of closure of the clamp arm 1 140) as the ultrasonic bladel 128 (FIG. 23) heats the tissue according to the collagen transformation point of the tissue.
  • a control algorithm is configured to close the clamp arm 1 140 until the clamp arm load reaches a threshold, which can include a particular value (e.g., 4.5 lbs.) or a range of values (e.g., within a range of 3.5 to 5 lbs.).
  • a threshold can include a particular value (e.g., 4.5 lbs.) or a range of values (e.g., within a range of 3.5 to 5 lbs.).
  • the control algorithm sets the clamp arm displacement rate of change threshold Q and monitors the displacement of the clamp arm 1 140. As long as the rate of change of the clamp arm displacement remains within a predefined negative limit (i.e. , below the threshold Q), the control algorithm can determine that the tissue is below the transformation temperature.
  • the control algorithm can determine that melt temperature of the collagen has been reached.
  • the control algorithm can be configured to alter the operation of the ultrasonic instrument accordingly.
  • the control algorithm can switch the surgical instrument from load control (of the clamp arm 1 140) to temperature control.
  • the control algorithm can maintain the load control of the clamp arm after the collagen transformation temperature has been reached and monitor for when a clamp arm displacement rate of change threshold has been reached.
  • the second clamp arm displacement rate of change threshold can correspond to, for example, the transition temperature of elastin.
  • the locations of the collagen and/or elastin transitions temperatures in the plot 130258 of the clamp arm displacement over time can be referred to a“knee” in the plot 130258.
  • control algorithm can be configured to alter the operation of the ultrasonic instrument according to whether the second clamp rate displacement rate of change threshold (or elastin “knee”) has been reached and alter the operation of the ultrasonic instrument accordingly.
  • the control algorithm can switch the surgical instrument from load control (of the clamp arm 1 140) to temperature control when the elastin knee in the plot 130258 is detected.
  • Collagen transformation should be constant for a given heat flux between 45° and 50°C for collagen, where elastin has a different melt temperature. Further, the temperature should flatten as the collagen absorbs the heat.
  • the control algorithm can be configured to sample the position of the clamp arm and/or clamp arm displacement member at a higher rate around particular temperatures or within temperature ranges (e.g., the ranges for expected temperature for collagen and/or elastin transformation) in order to precisely ascertain when the monitored events occur.
  • control algorithm acts to change the surgical instrument from load control to temperature control when the collagen transformation point is detected at time t m . Without changing the surgical instrument to temperature control, the clamp arm displacement would increase geometrically, as shown in the projected plot 130260.
  • control algorithm operating in temperature control mode lowers the amplitude of the ultrasonic transducer drive signal to change the heat flux generated by the ultrasonic blade 1 128, as shown by the flat portion of the plot 130258 after the threshold Q is reached.
  • control algorithm can be configured to increase the amplitude of the ultrasonic transducer drive signal after a particular period of time to, for example, measure the rate of temperature increase to determine when the elastin transformation temperature has been reached. Accordingly, as the clamp arm rate of closure approaches the next knee (i.e., the elastin knee) the clamp arm rate of closure can decrease. Load control of the clamp arm 1 140 can be beneficial because, in some cases, it can provide the best sealing of vessels.
  • FIG. 65 is a logic flow diagram of a process 130300 depicting a control program or a logic configuration to detect the collagen transformation point to control the rate of closure of the of the clamp arm or the amplitude of the ultrasonic transducer, in accordance with at least one aspect of the present disclosure.
  • the process 130300 can be executed by a control circuit or processor located in the surgical instrument or the generator. Accordingly, the control circuit executing the process 130300 measures 130302 a position of the clamp arm actuation member and its rate of change while maintaining the load on the clamp constant.
  • the load on the clamp arm is maintained within coaptation pressure within a suitable range (130-180 psi) set by the ultrasonic surgical instrument.
  • the control circuit sets 130304 the clamp arm displacement rate of change and monitors the position of the clamp arm actuation member for the period of time that the clamp arm displacement rate of change remains within a predefined negative limit (corresponding to the tissue being below the collagen transformation temperature). Accordingly, the control determines 130306 whether the clamp arm displacement rate of change exceeds the set threshold or, in other words, determines whether the tissue has reached the transition temperature.
  • the process 130300 proceeds along the YES branch and the control circuit switches 130308 the surgical instrument to temperature control (e.g., controls the ultrasonic transducer to decrease or maintain the temperature of the ultrasonic blade). In one aspect, the control circuit continues monitoring for the collagen transformation temperature. Alternatively, in the aspect depicted in FIG. 65, if the transition temperature has not been reached, then the process 130300 proceeds along the NO branch and the control circuit maintains 130310 the load control of the clamp arm 1 140 and monitors the clamp arm displacement rate of change to determine when the next transition point (e.g., the elastin transition point) occurs for the grasped tissue. The control circuit can do this in order to, for example, prevent the temperature of the tissue from increasing beyond the elastin transformation temperature.
  • the next transition point e.g., the elastin transition point
  • the collagen transformation should be constant for a given heat flux (45°C-50°C). It also will be appreciated that load control of the clamp arm 1 140 can, in some cases, provide the best sealing for particular types of tissues (e.g., vessels). During the period of time where collagen transformation is occurring, the temperature of the tissue should flatten while the collagen absorbs the heat.
  • the control circuit can be configured to modulate the rate at which data points are collected around a particular temperature or temperatures of interests (e.g., transformation temperatures). Further, the control circuit can tune the amplitude of the ultrasonic transducer drive signal to control the heat flux generated by the ultrasonic blade 1 128 at different points in the surgical procedure.
  • control circuit can decrease the ultrasonic transducer amplitude during the period of collagen transformation.
  • control circuit can increase the ultrasonic transducer amplitude to measure the rate at which the temperature increases when the elastin knee occurs. It will be appreciated that as the elastin knee is approached, the rate of temperature change will decrease.
  • a control algorithm can be configured to detect the collagen transformation temperature to identify the collagen/elastin percentage of the grasped tissue. As discussed above, the control algorithm can then control various operational parameters of the surgical instrument according to the identified composition of the grasped tissue.
  • FIG. 66 is a graphical representation 130350 of the identification of the collagen transformation temperature point to identify the collagen/elastin ratio, in accordance with at least one aspect of the present disclosure.
  • the vertical axis 130352 represents ultrasonic transducer impedance and the horizontal axis 130632 represents tissue temperature. The point at which the rate of change of the ultrasonic transducer impedance shifts corresponds to the
  • collagen/tissue composition of the tissue in an empirically determined manner. For example, if the rate of change of the ultrasonic transducer impedance shifts at the first temperature 130362, then the tissue composition is 100% collagen. Accordingly, if the rate of change of the ultrasonic transducer impedance shifts at the second temperature 130364, then the tissue composition is 100% elastin. If the rate of change of the ultrasonic transducer impedance shifts between the first temperature 130362 and the second temperature 130364, then the tissue composition is a mixture of collagen and elastin.
  • the collagen transformation temperature can be used to directly identify the collagen/elastin percentage in the tissue and a control algorithm can be configured to adjust the operation of the ultrasonic device accordingly.
  • a plot 130356 represents the empirical relationship between ultrasonic transducer impedance and tissue temperature.
  • the impedance (Z) of the ultrasonic transducer increases linearly at a first rate of change (slope) as a function of the temperature (T) at the tissue contact area.
  • the rate of change of impedance (Z) as a function of temperature (T) decreases to a second rate of change.
  • the collagen-to-elastin ratio can correspond to an empirically determined temperature 130360 (e.g., 85%).
  • a control circuit or processor executing the aforementioned algorithm can be configured to determine at what temperature the rate of ultrasonic transducer impedance changes and then retrieve the corresponding tissue composition (e.g., percentage of collagen, percentage of elastin, or collagen/elastin ratio) from a memory (e.g., a look-up table).
  • FIG. 67 is a logic flow diagram of a process 130450 for identifying the composition of a tissue according to the change in ultrasonic transducer impedance, in accordance with at least one aspect of the present disclosure.
  • the process 130450 can be executed by a control circuit of processor located in, for example, the surgical instrument or generator. Accordingly, the control circuit monitors 130452 the impedance (Z) of the ultrasonic transducer as a function of temperature (T). As previously described, the temperature (T) at the interface of the tissue and ultrasonic blade may be inferred by the algorithms described herein.
  • the control circuit determines 130454 the rate of change of the ultrasonic transducer impedance DZ/DT.
  • the control circuit determines 130456 whether the slope DZ/DT has changed (e.g., has decreased). If the slope DZ/DT has not changed, then the process 130450 proceeds along the NO branch and continues determining 130454 the slope DZ/DT. If the slope DZ/DT has changed, the control circuit determines 130458 that the collagen transition temperature has been reached.
  • the ratio of elastin to collagen may be determined by monitoring the collagen transformation point of the tissue and comparing the detected collagen transformation point to a look-up table.
  • the look-up table can be stored in memory (e.g., memory 3326 of FIG. 31 ) and contains the ratio of elastin to collagen and a corresponding collagen transformation point for a particular ratio as determined empirically.

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CN113274097B (zh) * 2020-11-03 2023-03-28 以诺康医疗科技（苏州）有限公司 用于结束组织剪切的超声刀自适应控制方法及系统
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