Medical device and related system and method for reducing signal distortion in image signal

Abstract

According to one aspect, the present disclosure is directed to a medical device system for visualizing an internal anatomy of a patient, the medical device system may include a shaft and a control unit operatively coupled to the shaft; the shaft comprises a distal tip portion, and the distal tip portion comprises an imaging device and a signal modulator; the control unit comprises a demodulator. The imaging device may be configured to output a first signal to the signal modulator. The signal modulator may be configured to modulate a received first signal and output a modulated second signal to the control unit; and the demodulator of the control unit may be configured to receive the modulated second signal, demodulate the second signal, and output a demodulated third signal. The control unit may be configured to output the demodulated third signal to an electronic display.

Description

Cross-reference to related applications

[0001] This application claims the benefit of priority to U.S. Provisional Patent Application No. 63 / 515,857, filed July 27, 2023, the entire contents of which are incorporated herein by reference. Technical Field

[0002] Various aspects of this disclosure relate generally to medical devices, particularly endoscopes including imaging elements, such as endoscopes or bronchoscopes. More specifically, embodiments of this disclosure relate to reducing noise and other signal distortions in the image signal of an imager in an endoscope or other medical device, and so on. Background Technology

[0003] Endoscopes have gained widespread acceptance in the medical field because they provide a way to perform surgery with minimal patient trauma while allowing doctors to visualize the patient's internal anatomy. Various endoscopes have been developed and categorized according to specific applications, such as cystoscopy, colonoscopy, laparoscopy, and upper gastrointestinal endoscopy. Endoscopes can be inserted into the body's natural orifices or through skin incisions.

[0004] Endoscopes are typically long, thin tubular shafts (rigid or flexible) with a camera or fiber optic lens assembly at their distal end. The shaft connects to a handle. Observation is made via an external screen. Various surgical instruments can be inserted through the working channel of the endoscope to perform different surgical procedures. Endoscopes currently in use (such as colonoscopes) typically have a front-mounted camera for viewing internal organs (such as the colon), an illuminator, a fluid injector for cleaning the camera lens (and sometimes also the illuminator), and a working channel for inserting surgical instruments (e.g., for removing polyps found in the colon). Endoscopes often also have a fluid injector (“jet”) for cleaning the body cavity into which they are inserted, such as the colon. Common illuminators are fiber optics and light-emitting diodes (LEDs) at the endoscope's distal end, with the fiber optic transmitting light generated remotely to the distal end of the endoscope.

[0005] Current endoscopes typically achieve imaging through a camera sensor located at the end of the endoscope, usually a charge-coupled device (CCD) sensor or a complementary metal-oxide-semiconductor (CMOS) sensor. Some cameras combine two or more sensor arrays to improve clarity and performance. However, image quality is not solely related to the camera sensor. The entire imaging chain must be optimized and coordinated. This includes lenses, endoscope optics, image signal transmission mechanisms, processing systems, monitors, and other components. Furthermore, the image recording mode (e.g., video or still image) plays a crucial role and can influence diagnostic values.

[0006] The acquired camera sensor data is transmitted to the video processing unit to be converted into an image. The video processor optimizes the image or real-time video according to selected preset parameters (e.g., white balance, color display mode, reflection reduction, or image rotation), and then transmits the image or real-time video to the screen. Furthermore, scenes and images can be stored for subsequent diagnostics or recording. In conjunction with different light sources, some video processors offer enhancement techniques such as narrowband imaging (NBI), autofluorescence (AF), or flexible spectral imaging color enhancement (FICE).

[0007] Before the signal is processed by the control unit, the raw analog signal data transmitted from the camera sensor at the endoscope's tip may have to travel several feet—for example, five feet or more along the length of the endoscope's axis and through the endoscope's umbilical cable. In smaller imaging systems used with smaller diameter endoscopes, such as bronchoscopes or cholangioscopes, the acquired camera sensor data may be the raw analog signal without any preprocessing at the endoscope's tip. This means that the raw analog signal is more susceptible to pickup noise as it travels the length of the endoscope and may also pass through the umbilical cable. Furthermore, other environmental factors can introduce additional noise into the signal.

[0008] There is a need in the art for image processing apparatuses, systems and methods that can be implemented in size and hardware-constrained medical devices, such as endoscopes, particularly smaller diameter endoscopes, and that also provide reduced noise in the camera signal. Summary of the Invention

[0009] This disclosure relates to systems, apparatuses, and methods for reducing noise in image signals from medical devices. The systems, apparatuses, and methods of this disclosure can help reduce noise in raw or processed image signals received from the distal end portion of an endoscope or other medical device. The systems, apparatuses, and methods of this disclosure can reduce the need for preprocessing of image signals at the distal end portion of the medical device, can facilitate a reduction in the size of the endoscope distal portion, can increase the clarity of medical images from the endoscope, and can help solve other problems. Each aspect disclosed herein may include one or more features described in conjunction with any of the other disclosed aspects.

[0010] According to one aspect, a medical device system for visualizing a patient's internal anatomy may include: an axis and a control unit operatively coupled to the axis; the axis includes a distal end portion including an imaging device and a signal modulator; the control unit includes a demodulator. The imaging device is configured to output a first signal to the signal modulator. The signal modulator is configured to modulate the received first signal and output a modulated second signal to the control unit; and the demodulator of the control unit is configured to receive the modulated second signal, demodulate the second signal, and output a demodulated third signal. The control unit is configured to output the demodulated third signal to an electronic display.

[0011] In other aspects, the medical device system may include one or more of the following features: A second signal may be transmitted to a demodulator via a single wire. The distal end portion may also include a low-pass filter. The distal end portion may also include a pulse generator. The distal end portion may also include pulse shaping circuitry. The control unit may include a holding circuit configured to receive the second signal. The control unit may also include a low-pass filter configured to receive the second signal from the holding circuit. The medical device may be an endoscope. The second signal may be transmitted to the demodulator via an antenna. The modulator may be configured to apply a carrier technology to the first signal to generate the second signal, and the carrier technology may include at least one of the following: amplitude modulation (AM), pulse amplitude modulation (PAM), pulse width modulation (PWM), frequency modulation (FM), or phase modulation (PM). The modulator may be configured to apply frequency modulation carrier technology and output the second signal with a 24 MHz bandwidth. The modulator may be configured to apply pulse amplitude modulation carrier technology. The modulator may be configured to apply phase modulation carrier technology. The first signal may have a frequency between 10 MHz and 99 MHz; and the modulator may be configured to apply a carrier pulse sequence at a frequency between (i) 2.5 times the frequency of the first signal and (ii) 5 times the frequency of the first signal. The second signal may be an integral of the first signal.

[0012] In other aspects, a medical device system for visualizing a patient's internal anatomy may include: a shaft and a handle operatively coupled to the shaft; the shaft includes a distal end portion comprising an imaging device and a signal modulator; the handle includes a demodulator. The imaging device may be configured to output a first signal to the signal modulator. The signal modulator may be configured to modulate the received first signal and output a modulated second signal to a control unit. The demodulator in the handle may be configured to receive the modulated signal, demodulate the second signal, and output a demodulated third signal; and the handle may be configured to output the third signal to an electronic display or a control unit.

[0013] In other aspects, the medical device system may include one or more of the following features: The distal end portion may include a low-pass filter. The distal end portion may include a pulse generator. The distal end portion may include pulse shaping circuitry.

[0014] In other respects, a method of operating a medical device (which includes a handle and a shaft extending longitudinally from the handle) includes: receiving a first signal from an imaging device at a modulator at a distal end portion of the shaft; transmitting a modulated second signal to a demodulator in the handle; and transmitting a demodulated third signal from the demodulator to a control unit.

[0015] It is understood that the foregoing general description and the following detailed description are merely exemplary and illustrative, and do not limit the claimed invention. Attached Figure Description

[0016] The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate exemplary aspects of this disclosure and, together with the description, serve to explain the principles of this disclosure.

[0017] Figure 1A and Figure 1B This is a perspective view of an exemplary endoscope according to various aspects of this disclosure.

[0018] Figure 2 An exemplary signal path is shown from the original analog imager signal to the signal cable carrier according to various aspects of this disclosure.

[0019] Figure 3 An exemplary signal path from a modulated image signal to a demodulated signal is shown according to various aspects of this disclosure.

[0020] Figures 4A to 4C Exemplary unmodified and modified signal waveforms are shown according to various aspects of this disclosure.

[0021] Figure 4D The diagram shows waveforms generated by pulse width modulation techniques according to various aspects of this disclosure.

[0022] Figure 5 An exemplary signal path is shown from the original analog imager signal to the transmitter (e.g., a single wire carrier) according to various aspects of this disclosure.

[0023] Figure 6 Exemplary imaging signal modulation techniques for use in medical devices are shown according to various aspects of this disclosure.

[0024] Figure 7 This is an example of an ultra-wideband phase modulation carrier technology with a high modulation index according to several aspects of this disclosure.

[0025] Figure 8 Exemplary phase modulation schemes according to various aspects of this disclosure are shown. Detailed Implementation

[0026] Reference will now be made in detail to several aspects of this disclosure, examples of which are illustrated in the accompanying drawings. Where possible, the same or similar reference numerals will be used in the drawings to refer to the same or similar parts. The term “distal” refers to the part furthest from the user when the device is introduced into the patient. In contrast, the term “proximal” refers to the part closest to the user when the device is placed inside the patient. In all the figures included in this application, arrows labeled “P” and “D” are used to indicate the proximal and distal directions in the figures. As used herein, the terms “comprising,” “including,” “containing,” “having,” or any other variation thereof are intended to cover a non-exclusive inclusion, such that a process, method, article of manufacture, or apparatus that includes a list of elements may include not only those elements but also other elements not expressly listed or inherent to such a process, method, article of manufacture, or apparatus. The term “exemplary” is used in the sense of “example” rather than “ideal.” Additionally, relative terms (such as, for example, “about,” “comparatively,” “approximately,” etc.) are used to indicate possible variations of ±10% in the stated values ​​or ranges.

[0027] Embodiments of this disclosure can improve the image quality of image signals from medical devices (such as endoscopes) during medical procedures; and, as a non-limiting exemplary benefit, can help improve the visual display of cameras or other imaging systems in medical devices. Embodiments of this disclosure can also particularly help reduce noise and other signal distortions in image signals from medical devices.

[0028] Figure 1A and Figure 1BA perspective view of an exemplary endoscope system 100 is shown. The endoscope system 100 may include an endoscope 101. The endoscope 101 may include a handle assembly 106 and a flexible tubular shaft 108. The handle assembly 106 may include a biopsy port 102, a biopsy cap 103, an image capture button 104, a lift actuator 107, a first locking lever 109, a second locking lever 110, a first control knob 112, a second control knob 114, a suction button 116, an air / water button 118, a handle body 120, and an umbilicus 105. All actuators, lifters, knobs, buttons, levers, ports, or caps of the endoscope system 100 (such as those listed above) may be used for any purpose and are not limited to any particular use, which may be implied by the appropriate naming of each component as used herein. The umbilicus 105 may extend from the handle body 120 to one or more auxiliary devices, such as a control unit 199, a water / fluid supply, and / or a vacuum source. Therefore, the umbilicus 105 may transmit signals between the endoscope 101 and the control unit 199 to control the illumination and imaging components of the endoscope 101, and / or to receive image data from the endoscope 101. The umbilicus 105 may also provide fluid from the water / fluid supply for irrigation and / or to provide suction to the distal end 119 of the shaft 108. Buttons 116 and 118 control valves for suction and fluid supply (e.g., air and water), respectively. The shaft 108 may terminate at the distal end 119. The shaft 108 may include a hinged segment 122 for deflecting the distal end 119 in upward, downward, leftward, and / or rightward directions. Knobs 112 and 114 can be used to control such deflection, and locking levers 109 and 110 can lock knobs 112 and 114 in the desired positions, respectively. The handle body 120 may be wedge-shaped and may narrow as the handle extends distally, such that the shape of the handle body 120 is smaller at its distal end than at its proximal end.

[0029] Although the term endoscope may be used herein, it should be understood that other devices (including, but not limited to, cholangioscopes, duodenoscopes, colonoscopes, ureteroscopes, bronchoscopes, laparoscopes, sheaths, catheters, or any other suitable delivery or medical devices) may be used in conjunction with the devices disclosed herein, and the devices, systems, and methods discussed below may be incorporated into any of these or other medical devices.

[0030] The distal end 119 may include an imaging device 222 (e.g., an image sensor, a camera, an optical fiber, a lens assembly with an image sensor, etc.) and at least one light source 223 (e.g., an LED or an optical fiber). Figure 2 As shown. In some instances, the distal end 119 may include a forward imaging device 222 (such as...). Figure 2As shown, it may include a forward imaging device 222 and a lateral imaging device 222, or may include only the lateral imaging device 222, or may include a forward imaging device 222 and two lateral imaging devices 222, or any other combination of imaging devices at the distal end 119. The lateral imaging device 222 and the light source 223 may face radially outward, vertically, substantially vertically, or otherwise transverse to the axis 108 and / or the longitudinal axis of the distal end 119. The forward or forward-facing imaging device 222 or the light source 223 may face substantially along or parallel to the longitudinal axis of the distal end 119 and the axis 108. In some instances, the imaging device 222 may be a charge-coupled device (CCD) image sensor, a complementary metal-oxide-semiconductor (CMOS) image sensor, and / or any other element for converting light into electrons that are transmitted as electrical signals.

[0031] The control unit 199 is capable of docking with the endoscope 101 to provide power and / or commands to the imaging device 222 and / or the light source 223. The control unit 199 may also control one or more other aspects of the endoscope 101, such as, for example, the application of suction, the deployment or delivery of fluid, and / or the movement of the distal end 119. The control unit 175 may be powered by an external source, such as an electrical outlet. Furthermore, the control unit 175 may include or be otherwise coupled to one or more buttons, knobs, touchscreens, or other user interfaces to control the imaging device 222, the light source 223, and other features of the endoscope 101. The control unit 199 may be housed within the handle 106 itself or in a separate device.

[0032] Control unit 199 may be configured to allow a user to set or control one or more illumination and imaging parameters. For example, control unit 199 may allow a user to set or control the illumination level of each light source 223, the gain level of each imaging device 222, the exposure time of each imaging device 222, the frame rate of each imaging device 222, a maximum or target value of any of the illumination and imaging parameters, and / or any other parameters associated with the imaging device 222 and / or the light source 223. In some instances, control unit 199 may be configured to perform one or more algorithms using one or more illumination and imaging parameters, such as to automatically adjust the illumination level of one or more light sources 223 and / or to automatically adjust one or more parameters of the imaging device 222. For example, control unit 199 may set or select the illumination level of one or more light sources 223 based on data received from one or more imaging devices 222. In some instances, as will be discussed in more detail below, control unit 199 may demodulate one or more image signals received from the imaging device 222.

[0033] Control unit 199 may include electronic circuitry configured to receive, process, and / or transmit data and signals between endoscope 101 and one or more other devices. For example, control unit 199 may electronically communicate with a display configured to display an image generated by imaging device 222 of endoscope 101 based on image data and / or signals processed by control unit 199. Control unit 199 may communicate electronically with the display in any suitable manner, via wired or wireless means. The display may be manufactured in any suitable manner and may include a touchscreen input and / or be connectable to various input and output devices, such as, for example, a mouse, stylus, printer, server, and / or other portable electronic devices. Control unit 199 may include software and / or hardware that facilitates operations such as those discussed above. For example, control unit 199 may include one or more algorithms, models, etc., for performing any of the methods and / or systems discussed in this disclosure. The control unit 199 can be configured to automatically adjust the illumination value applied to one or more light sources 223, and automatically adjust the gain and frame rate applied to one or more imaging devices 222.

[0034] When operating the endoscope system 100, the user can use his / her left hand to hold the handle assembly 106. Figure 2 (As shown in A), while simultaneously gripping one or more actuators of the accessory device and / or operating handle assembly 106 with the right hand, such as the first control knob 112 and the second control knob 114, and the first locking lever 109 and the second locking lever 110. The user can grasp the handle assembly 106 by wrapping their hand around the handle body 120. When grasping the handle body 120, the user can use their left thumb to operate the first control knob 112 and the second control knob 114, as well as the lift actuator 107 (by rotating it about its respective axis), and can use their left-hand fingers to operate the image acquisition button 104, the suction button 116, and / or the air / water button 118 (each by pressing). The user can rotate the handle assembly 106 (e.g., by moving their wrist) to rotate the shaft 108 about its longitudinal axis and position the distal end 119 at a target area within the patient's body. The user can actuate button 104 to activate the video display of imaging device 222, to take photographs (such as digital photographs) with imaging device 222, and / or to take any other actions associated with imaging device 222. During operation, the user can view the video feed of imaging device 222 on electronic display 198. The real-time signal of imaging device 222 can be processed by control unit 199 and output to electronic display 198. Electronic display 198 may be one or more electronic displays, such as, for example, a monitor, television, tablet computer, smartphone, part of control unit 199, virtual reality display, or other display device.

[0035] In some instances, the imaging device 222 at the distal end of an endoscope (particularly a small-diameter endoscope) may consist solely of an image sensor (such as a CCD or CMOS sensor) without any other image processing components, and may output an image signal of the raw voltage data acquired by the image sensor. Such a signal may be susceptible to noise along the length of the endoscope 101 and may also be susceptible to noise caused by other environmental factors. By modulating the raw image signal from the image sensor, noise can be reduced, and the signal can be less susceptible to signal distortion as it travels along axis 108.

[0036] Figure 2 A flowchart illustrating the process of modulating the original analog imager signal and transmitting it on a single wire carrier is shown, such as transmitting via a single wire extending along the length of axis 108, through shank 106, and through umbilicus 105 to control unit 199. Figure 2 As shown, the raw analog signal 250 can be output from the imaging device 222 at the distal portion 119 of the endoscope 101. The raw analog signal 250 can be in the form of a voltage signal provided from a CCD image sensor, a CMOS sensor, or any other suitable image sensor; and is shown as a graph of the sensor's voltage output versus time (T). Figure 3 The example graph of the raw analog signal 250 shows values ​​Tc, Tb, Td, and TP specific to Omnivision analog sensors. The width of Tc informs the signal processor of the type of information being transmitted in subsequent signals. For example, a value of Tc might indicate that the subsequent signal contains the value of a blue pixel in a row. Tb represents the black level of that row, Td is the value of a pixel in that row, and TP indicates the end of that row. In some instances, Tc might represent a start pulse or clock cycle, Tb might represent a "blank level" cycle, Td might represent the raw analog cycle, and TP might be the end cycle that begins with a transition through the blank level. Other analog sensors may have similar signals, containing only signals such as Tc and Td, or any other combination of these values. The raw analog signal 250 can be output to a modulator 251 within the distal portion 119 of axis 108 to modulate the raw analog signal 250.

[0037] The process by which one of the characteristic parameters (amplitude, frequency, phase, etc.) of a carrier signal changes linearly relative to the amplitude of the message signal is called modulation. Figure 2 In the application shown, the message signal is the raw signal output from imaging device 222, and the carrier signal is the modulated signal 253, 254 output from modulator 251. Carrier technology 252 is applied by modulator 251 to the raw analog signal 250 to generate modulated signals 253, 254. Note that examples of modulated signals 370, 371 are shown as follows: Figure 3The modulated signal waveform in the image. Various forms of modulation exist, each designed to alter specific characteristics of the carrier signal wave. The most commonly altered characteristics include amplitude, frequency, phase, pulse sequence, and pulse duration. For example... Figure 2 As shown, the carrier technology can be amplitude modulation (AM), pulse amplitude modulation (PAM), pulse width modulation (PWM), frequency modulation (FM), phase modulation (PM), and any other carrier technology known in the art, such as digital modulation (DM), pulse code modulation, frequency shift keying, or amplitude shift keying. The modulator 251 within the distal end portion 119 can be any modulator known in the art, such as a sigma-delta modulator or a silicon carbide electro-optic modulator; and can be implemented on a circuit board within the distal end portion 119 of the endoscope 101 or on any other modulator device known in the art. The type of modulator will depend on the modulation scheme used. For example, a simple FM transmitter would be used for frequency-modulated signals. The circuitry varies based on the modulation type. In some instances, quadrature amplitude modulation (QAM) may be used.

[0038] As discussed above, after the original analog signal 250 is modulated by modulator 251, modulated signals 253 and 254 are output to cables extending through shaft 108 and handle 106 to control unit 199, multiple cables extending through endoscope 101, or output to an antenna or other wireless transmission device wirelessly transmitted to control unit 199, a receiver within handle 106, or any other device for demodulation and processing. In some instances, the antenna or other wireless transmission device may be located within end portion 119, within another portion of shaft 108, within handle 106, and / or within any other portion of medical device system 100. In some instances, one or more cables may connect imaging device 222 and / or modulator 251 to an antenna located within shaft 108 or handle 106.

[0039] Figure 3 A flowchart illustrating the process for demodulating the modulated image signal 360 is shown, such as... Figure 2 The process flow diagram shown represents modulated image signals 253 and 254. Specifically, Figure 3The demodulation of modulated image signals 253, 254, 360 in a handle 306 (which in some instances may be the handle 106 of an endoscope 101) is shown to restore the modulated image signals 253, 254 to the original analog signal 250 of the imaging device 222. The demodulator 361 may be located within the handles 306, 106 and may be any demodulator known in the art, such as electronic circuitry or computer programs present on one or more processors within the handle 106. Any one or more methods for demodulation may be implemented on the demodulator 361, such as utilizing a synchronization detector, frequency modem, phase modem, envelope detector, product detector, quadrature detector, Foster-Selly discriminator, carrier recovery, clock recovery, bit slip, frame synchronization, rake receiver, pulse compression, received signal strength indication, error detection and correction, or any combination of these demodulation methods and / or other demodulation methods known in the art. After demodulation by demodulator 361 within handles 306 and 106, the original analog signal 250 can be output to control unit 199, for example, via wireless transmission, via umbilicus 305, or any other transmission means. In some instances, demodulator 361 may be located within shaft 108, within umbilicus 105 and 305, within connector 366 of umbilicus 305, or within control unit 199. After demodulation, the original analog signal 250 can be processed and displayed by control unit 199, for example, by outputting a processed image signal to electronic display 198.

[0040] Figures 4A to 4C The diagram illustrates applying a carrier pulse sequence 401 (e.g., applied via modulator 251) to a carrier signal 402 (such as the original analog imaging signal 250) to generate a pulse amplitude modulated output signal 403. The pulse amplitude modulated output signal 403 can be output from modulator 251 to a single wire extending through shaft 108, multiple wires extending through shaft 108, an antenna located at end portion 119, or a waveguide located at end portion 119. In some examples, imaging device 222 ( Figure 2 The original analog signal 250 can be output at frequencies of tens of megahertz, such as any frequency between 10 MHz and 99 MHz (inclusive); and the frequency of the carrier pulse sequence 401 can be at least 2.5 times higher than the frequency of the original analog signal 250. For example, the frequency of the carrier pulse sequence 401 can be at least between 25 MHz and 247.5 MHz (inclusive); and the carrier pulse sequence 401 can not exceed 5 times the frequency of the original analog signal 250, or, depending on the frequency of the original analog signal 250, can not exceed between 50 MHz and 495 MHz. The frequency of the carrier pulse sequence 401 can be designed to satisfy the Nyquist sampling theorem requirement while limiting the possibility of picking up erroneous noise spikes from the interface connection between the imaging device 222 and the modulator 251.

[0041] Figure 4D An example of pulse width modulation (PWM) is shown, including the original analog signal 250, shown as a solid line (V), and the PWM-modulated signal, shown as a dashed line (B). In PWM, the modulating signal can be the integral of the original analog signal 250. In some instances, PWM can be used to modify the output load of the imaging device 222; this can help reduce noise in the output signal as the modulated signal travels through axis 108.

[0042] To further reduce noise in the signal from the imaging device 222, a low-pass filter (LPF) can be incorporated. Figure 2 and Figure 3 The signal processing flow is shown. Figure 5 A flowchart 500 illustrates the signal modulation process of the imaging device 222, including a low-pass filter (LPF) 502. Specifically, Figure 5 The process flowchart shown utilizes a modulator 503 employing pulse amplitude modulation technology, where a pulse generator 504 modulates a message signal 501, such as the raw data signal from the imaging device 222. Figure 5 As shown, before the signal is sent to modulator 503, message signal 501 is first sent to low-pass filter 502. Low-pass filter 502 may be located within the distal segment 119 of endoscope 101. In other instances, the modulated signal may be sent through shaft 108 and then to a low-pass filter located in handle 106 or control unit 199. In other instances, the signal processing flow may include both low-pass filter 502 located in distal segment 119 and another low-pass filter located in handle 106 and / or control unit 199. Low-pass filter 502 may include a signal cutoff point close to the highest frequency of imaging device 222 to eliminate any high-frequency noise spikes that the system may pick up. For example, if the highest output frequency of imaging device 222 is 300 MHz, then low-pass filter 502 may have a cutoff point set to 301 MHz. In some instances, the system may filter out signals from 88 MHz to 108 MHz, as this band is the US FM band. In some instances, the signal can be transmitted at a frequency of 915 MHz or 868 MHz. In some instances, the conduit length of the device (e.g., the length of shaft 108) can be several times a quarter wavelength of the carrier frequency, which is beneficial for impedance matching.

[0043] The pulse shaping circuit 505 can also be located within the end portion 119 and can be used to shape the modulated signal into a modulated pulse sequence signal, such as a pulse amplitude modulation (PAM) signal. (See reference) Figure 5The message signal 501 can be output from the imaging device 222 to a low-pass filter 502 (e.g., located within the end portion 119), and the output of the low-pass filter 502 can then be sent to a modulator 503. A pulse generator 504 provides pulses to the modulator 503. The signal from the pulse generator 504 (e.g., at the end portion 119) can be modulated by the message signal 501 in the modulator 503, and the output of the modulator 503 can then be sent to a pulse shaping circuit 505. The pulse shaping circuit 505 can shape the pulses of the modulated signal to allow a receiver (such as a demodulator 361) to easily detect the pulse amplitude modulation signal 506. Figure 5 Any of the components shown may be incorporated into a single circuit board, multiple circuit boards, or any other device known in the art; and may be located within the end portion 119 or a portion of the shaft 108.

[0044] Figure 6 A process flow diagram of an exemplary demodulator 600 is shown. The exemplary demodulator 600 may be located within the handle 106, the control unit 199, the umbilicus 105, or the shaft 106; and may be configured to receive modulated imaging signals from the imaging device 222, for example from... Figure 5 The PAM signal generator shown. The received PAM signal 601 (which may be PAM signal 506 sent from pulse shaping circuit 505) may be received by holding circuit 602. Holding circuit 602 may include at least one capacitor configured to charge to the pulse amplitude value of PAM signal 601; and may be configured to hold the amplitude value during the interval between pulses of PAM signal 601. In some instances, holding circuit 602 may be a zero-order holding circuit, which considers only the previously sampled value to determine the value between two pulses. Figure 6 As shown, the output of the holding circuit 602 can be sent to the low-pass filter 603 to smooth the demodulated signal 604. The demodulated signal 604 can then be sent to the control unit 199 for processing (e.g., via a processor) and / or displayed on the electronic display 198.

[0045] In some instances, the signal from imaging device 222 can be modulated using frequency modulation, such as ultra-wideband frequency modulation. Because the medical device system described herein (such as medical device system 100) is a closed system (with a point-to-point or direct-line link between the transmitter and receiver of the imaging signal), ultra-high-bandwidth frequency modulation carrier technology that provides the ultra-wideband carrier signal can be implemented in this system without considering adjacent channel interference or broadcast frequencies.

[0046] Figure 7 Graph 701 shows an example of an ultra-wideband frequency modulation spectrum with a high modulation index. (As shown...) Figure 7As shown, the bandwidth of the modulated signal can be 24 MHz. When frequency modulation is implemented in the modulator 251 of the imaging device 222, the carrier technique used by the modulator 251 can follow the Carson bandwidth rule to meet the approximate bandwidth requirements for the carrier signal using frequency modulation. In some instances, the imaging device 222 can output an imaging signal from a 4 MHz clock system sampled at 8 MHz, thus having a frequency bandwidth of twice the peak offset (Δf = 4 MHz) and twice the highest frequency (fmm = 8 MHz); for ultra-wideband frequency-modulated carrier signals, the Carson bandwidth criterion would require a bandwidth of 24 MHz. The Carson bandwidth criterion can be defined as CBR = 2(Δf + fmm). By utilizing ultra-wideband frequency-modulated carrier techniques, the imaging signal of the imaging device 222 can have reduced noise as it travels to the handle 106 and / or control unit 199. In addition to reducing noise, modulation also allows the signal to travel over longer distances without signal degradation.

[0047] Figure 8 An exemplary phase modulation scheme 800 is illustrated, which can be applied using modulator 251 to the original analog signal 250 or any other imaging signal described herein. For phase modulation, the instantaneous amplitude of the analog signal 250 of imaging device 222 modulates the phase of a carrier signal (modulated carrier signal 253) to maintain its amplitude and frequency constant. When implementing phase-modulated carrier technology, the phase of the modulated carrier signal 253 is modulated to follow the changing signal level (amplitude) of the analog signal 250. The peak amplitude and frequency of the modulated carrier signal 253 remain constant, but as the amplitude of the analog signal 250 changes, the phase of the modulated carrier signal 253 changes accordingly. Figure 8 As shown, modulation waveform 802 is applied to carrier waveform 801, which can be the original analog signal 250 of imaging device 222. After modulator 251 applies modulation waveform 802 to carrier waveform 801 (e.g., analog signal 250), modulator 251 can output waveforms, such as phase-modulated waveform 803 of carrier waveform 801. The phase of phase-modulated waveform 803 can change with the amplitude of carrier waveform 801. By modulating the analog signal 250 of imaging device 222, the modulated signal can have reduced noise after transmission compared to transmitting the unmodulated analog signal 250. The carrier signal is given by c(t) = A c cos(w c t + phi) represents, where w c = 2 × pi × frequency, A c Let be the amplitude, phi be the phase, and t be the time. When a modulated signal is applied, the formula becomes s(t) = A c cos(w c t + k pm(t)), where m(t) is the message signal (e.g., an analog sensor), and k p This is the phase sensitivity. If m(t) = A m cos(w m If t), then s(t) = A c cos(w c t)+Bcos(w m t), where B = k p ×A m =Δphi. Δphi is the phase offset. Figure 8 An example of the previously derived derivation is shown.

[0048] During the operation of endoscope 101, the user can first actuate imaging button 104 to initiate imaging or video recording using imaging device 222. In some instances, the user can also actuate illuminator 223 to illuminate the field of view of imaging device 222. Imaging device 222 can then receive photons within its field of view at its image sensor and transmit the raw analog signal 250 to modulator 251 within the distal portion 119 of endoscope 101. Modulator 251 can then apply carrier technology 252 to the raw analog signal 250 to generate modulated imaging signal 253. As described above, any carrier technology, such as amplitude modulation (AM), pulse amplitude modulation (PAM), pulse width modulation (PWM), frequency modulation (FM), phase modulation (PM), or any other carrier technology, can be applied to the raw analog signal 250. The modulation signals 253, 254 can then be output to one or more wires extending through the shaft 108 to the handle 106, or to an antenna or other wireless transmission mechanism within the end portion 116, to transmit the modulation signals 253, 254 to the handle 106 or the control unit 199. The modulation signals 253, 254 can then be received by a demodulator 361 to convert the modulation signal 253 into an analog signal 250. In some instances, the analog signal 250 can then be transmitted from the handle 106 to the control unit 199 for processing and display by the electronic display 198. In other instances, the analog signal 250 can be demodulated and processed at the control unit 199 and displayed by the electronic display 198.

[0049] It will be apparent to those skilled in the art that various modifications and variations can be made to the disclosed systems, apparatus, and methods without departing from the scope of this disclosure. Other aspects of this disclosure will be apparent to those skilled in the art in light of the practice of the specification and the features disclosed herein. It is contemplated that the specification and embodiments be considered exemplary only.

Claims

1. A medical device system for visualizing the internal anatomy of a patient, the medical device system comprising: A shaft having a distal end portion, the end portion comprising: Imaging device, and Signal modulator; and A control unit operatively coupled to the shaft and including a demodulator; The imaging device is configured to output a first signal to the signal modulator; The signal modulator is configured to modulate the received first signal and output the modulated second signal to the control unit; The demodulator of the control unit is configured to receive the modulated second signal, demodulate the second signal, and output the demodulated third signal; and The control unit is configured to output the demodulated third signal to an electronic display.

2. The medical device system of claim 1, wherein the second signal is transmitted to the demodulator via a single wire.

3. The medical device system according to any one of the preceding claims, wherein the distal end portion further includes a low-pass filter.

4. The medical device system according to any one of the preceding claims, wherein the distal end portion further includes a pulse generator.

5. The medical device system according to any one of the preceding claims, wherein the distal end portion further includes a pulse shaping circuit.

6. The medical device system according to any one of the preceding claims, wherein the control unit further comprises a holding circuit configured to receive the second signal.

7. The medical device system of claim 6, wherein the control unit further comprises a low-pass filter configured to receive the second signal from the holding circuit.

8. The medical device system according to any one of the preceding claims, wherein the medical device is an endoscope.

9. The medical device system according to any one of the preceding claims, wherein the second signal is transmitted to the demodulator via an antenna.

10. The medical device system according to any one of the preceding claims, wherein the modulator is configured to apply a carrier technology to the first signal to generate the second signal, wherein the carrier technology includes at least one of: amplitude modulation (AM), pulse amplitude modulation (PAM), pulse width modulation (PWM), frequency modulation (FM), or phase modulation (PM).

11. The medical device system according to any one of the preceding claims, wherein the modulator is configured to apply frequency modulation carrier technology and output a second signal with a 24 MHz broadband frequency.

12. The medical device system of claim 1, wherein the modulator is configured to apply pulse amplitude modulation carrier technology.

13. The medical device system of claim 1, wherein the modulator is configured to apply phase modulation carrier technology.

14. The medical device system of claim 12, wherein the first signal has a frequency between 10 MHz and 99 MHz; and wherein the modulator is configured to apply a carrier pulse sequence at a frequency between (i) 2.5 times the frequency of the first signal and (ii) 5 times the frequency of the first signal.

15. The medical device system according to any one of the preceding claims, wherein the second signal is an integral of the first signal.

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