US20160284441A1 - Low noise cable providing communication between electronic sensor components and patient monitor - Google Patents
Low noise cable providing communication between electronic sensor components and patient monitor Download PDFInfo
- Publication number
- US20160284441A1 US20160284441A1 US15/003,747 US201615003747A US2016284441A1 US 20160284441 A1 US20160284441 A1 US 20160284441A1 US 201615003747 A US201615003747 A US 201615003747A US 2016284441 A1 US2016284441 A1 US 2016284441A1
- Authority
- US
- United States
- Prior art keywords
- wires
- cable
- low noise
- emitter
- detector
- Prior art date
- Legal status (The legal status 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 status listed.)
- Abandoned
Links
Images
Classifications
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B11/00—Communication cables or conductors
- H01B11/02—Cables with twisted pairs or quads
- H01B11/06—Cables with twisted pairs or quads with means for reducing effects of electromagnetic or electrostatic disturbances, e.g. screens
- H01B11/08—Screens specially adapted for reducing cross-talk
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B11/00—Communication cables or conductors
- H01B11/02—Cables with twisted pairs or quads
- H01B11/04—Cables with twisted pairs or quads with pairs or quads mutually positioned to reduce cross-talk
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B1/00—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors
- H01B1/02—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors mainly consisting of metals or alloys
- H01B1/026—Alloys based on copper
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B11/00—Communication cables or conductors
- H01B11/02—Cables with twisted pairs or quads
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B11/00—Communication cables or conductors
- H01B11/18—Coaxial cables; Analogous cables having more than one inner conductor within a common outer conductor
- H01B11/1895—Particular features or applications
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B13/00—Apparatus or processes specially adapted for manufacturing conductors or cables
- H01B13/02—Stranding-up
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B13/00—Apparatus or processes specially adapted for manufacturing conductors or cables
- H01B13/22—Sheathing; Armouring; Screening; Applying other protective layers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/18—Shielding or protection of sensors from environmental influences, e.g. protection from mechanical damage
- A61B2562/182—Electrical shielding, e.g. using a Faraday cage
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/22—Arrangements of medical sensors with cables or leads; Connectors or couplings specifically adapted for medical sensors
- A61B2562/221—Arrangements of sensors with cables or leads, e.g. cable harnesses
- A61B2562/222—Electrical cables or leads therefor, e.g. coaxial cables or ribbon cables
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/22—Arrangements of medical sensors with cables or leads; Connectors or couplings specifically adapted for medical sensors
- A61B2562/225—Connectors or couplings
- A61B2562/227—Sensors with electrical connectors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B7/00—Insulated conductors or cables characterised by their form
- H01B7/17—Protection against damage caused by external factors, e.g. sheaths or armouring
- H01B7/18—Protection against damage caused by wear, mechanical force or pressure; Sheaths; Armouring
- H01B7/182—Protection against damage caused by wear, mechanical force or pressure; Sheaths; Armouring comprising synthetic filaments
- H01B7/1825—Protection against damage caused by wear, mechanical force or pressure; Sheaths; Armouring comprising synthetic filaments forming part of a high tensile strength core
Definitions
- the present disclosure generally relates to patient monitoring devices and more specifically, embodiments of the present disclosure relate to cables connecting a monitor and a sensor of the patient monitoring device.
- Physiological measurement systems using spectroscopic analysis are a widely accepted noninvasive procedure for measuring patient characteristics such as oxygen and glucose levels. Measuring these characteristics is important for patient wellness because for instance, an insufficient supply of oxygen can result in brain damage and death in a matter of minutes. Thus, early detection of low blood oxygen level is of crucial importance in the medical field, especially in critical care and surgical applications.
- Patient monitors commercially available from Masimo Corporation of Irvine Calif., USA, measure many physiological parameters including oxygen saturation, pulse rate, perfusion, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, overall wellness, respiration, combinations of the same and others.
- a physiological measurement system consists of a monitor 101 , a noninvasive optical sensor 115 applied to a patient, and a cable 111 connecting the sensor and the monitor.
- the system is controlled using input keys.
- the monitor 101 may be a portable standalone device or may be incorporated as a module or built-in portion of a multiparameter patient monitoring system.
- the monitor displays measurements of various physiological patient characteristics on a display 105 , which may include an oxygen saturation level, a pulse rate, and an audible indication of each pulse via a speaker 107 .
- the monitor 101 may display the patient's plethysmograph, which is a visual display of the patient's pulse contour and pulse rate, as well as a myriad of other measurements and calculated parameters.
- the monitor 101 energizes one or more emitters in the sensor 115 that irradiate tissue under observation, such as, for example, a finger, toe, foot, hand, ear, forehead or the like.
- the radiation from the emitters is scattered and absorbed by the tissue such that some attenuated amount emerges and is detected through one or more detectors located in the sensor 115 .
- the detector(s) produces one or more signal(s) indicative of the intensity of the detected attenuated radiation and forward the signal(s) to the patient monitor 101 for processing.
- the sensor 115 that houses the emitters and the detectors can be disposable, reusable, or partially reusable and disposable.
- Reusable sensor may include a clothespin-shaped housing that includes a contoured bed conforming generally to the shape of a finger.
- the emitter and detector signals are transmitted over the cable 111 connecting the monitor and the sensor.
- cables can be affected by a phenomenon known as crosstalk.
- Crosstalk occurs when energy from one signal interferes with another signal. Such interference can cause significant distortion in the transmission of information which can lead to incorrect measurements in physiological monitoring applications.
- the cable 111 may unfortunately cause unwanted interference on the sensitive detector signals used to determine measurements of the physiological parameters.
- the present disclosure provides a low noise tinsel cable arrangement particularly suited for transmitting communications between devices.
- the cable is used to transmit electrical signals between a physiological sensor and a physiological monitor.
- the cable has one or more emitter wires configured to communicate drive signals between a monitor and at least one emitter.
- the cable also has one or more detector wires configured to communicate a physiological signals between at least one detector and the monitor.
- the emitter wires transmit relatively high energy drive signals, while the detector wires transmit lower energy physiological signals. Due to the effect of crosstalk, the high energy drive/emitter signals can distort the lower energy physiological/detector signals.
- the lower energy detector signal is an unknown signal.
- the unknown detector signal carries the important physiological patient information, such as, for example, signals responsive to absorption signals from the detector. Often, such absorption signals are lower energy signals and thus, often are more easily distorted. Thus, reducing interference with the detector signals improves system accuracy and reliability.
- the present disclosure describes mitigating crosstalk by twisting the emitter wires about the central axis of the cable in an opposing rotational direction relative to the detector wires.
- Opposing twists advantageously seeks to create an angle between the two functionally different wires that approaches 90 degrees. At such an angle, crosstalk is reduced without requiring heavy shielding.
- One embodiment twists the detector wires in one direction down the center of the cable.
- the detector wires are insulated with an inner shield.
- the emitter wires are twisted in another direction around the inner shield such that the angle between the emitter wires and the detector wires is about 90 degrees.
- the detector wires are twisted clockwise and the emitter wires are twisted counterclockwise, or vice versa.
- the emitter wires are insulated with an outer shield, and a jacket is disposed over the outer shield to form the cable.
- the disclosed opposing rotation of the wires mitigates crosstalk from the opposing rotation. This may be without or in addition to different twist rates or shielding. Opposing rotation in the cable structure may provide a more flexible cable, thereby not hindering sensor placement of the patient.
- tinsel wires are used to form the cable.
- Tinsel wires are relatively thin and strong. Using tinsel wires allows the cable to be lighter and more flexible than equivalent all metal wires. While thinner wire is advantageous in some respects, reducing the cable diameter also increases the resistance through the wires.
- the tinsel wires may also transmit the high energy drive signals. In such embodiments, the increasing resistance places some limitations on how small the cable diameter can be. The present disclosure accomplishes satisfactory signal transmission while simultaneously reducing the cable diameter.
- FIG. 1A illustrates a perspective view of a physiological measurement system utilizing a noninvasive optical sensor.
- FIG. 1B illustrates a perspective view of a portable physiological measurement system utilizing a noninvasive optical sensor.
- FIG. 2 illustrates a perspective view of an embodiment of an uncoated tinsel cable.
- FIG. 3 illustrates a perspective view of an embodiment of a coated tinsel cable.
- FIG. 4 illustrates a cross sectional view of an embodiment of a low noise patient cable.
- FIG. 5 illustrates a top-down view of an embodiment of the cable of FIG. 4 .
- FIG. 6 illustrates a cross sectional view of an embodiment of a low noise patient cable.
- FIG. 7 illustrates a block diagram of a simplified embodiment of a kink testing apparatus for a cable.
- FIG. 8 illustrates the testing apparatus of FIG. 7 with the cable in a stretched position.
- a physiological measurement systems 100 includes a monitor 101 , a cable 111 , and a sensor 115 .
- the sensor 115 can be any type of physiological sensor. Illustrated in FIGS. 1A and 1B are embodiments of noninvasive optical sensors.
- the monitor 101 sends drive signals to one or more emitters in the sensor 115 via the cable 111 .
- the emitters irradiate tissue under observation.
- One or more detectors in the sensor 115 detect the radiation leaving the tissue and send a signal back to the monitor via the cable responsive to the attenuation. This sequence produces more accurate results when the noninvasive optical sensor 115 remains substantially fixed with respect to the tissue of the patient.
- the senor 115 comprises a reusable sensor
- the sensor 115 is often held in place by only the spring action of a clothespin-shaped housing.
- the torque from the stiff or heavy cable may be more than the tension provided by the spring, thus even slightly shifting the optical components with respect to the measurement site on the tissue. A shifted or dislodged sensor could lead to erroneous physiological patient information.
- a stiff or bulky cable may be the result of utilizing heavy shielding to reduce damaging crosstalk.
- Crosstalk occurs when the drive/emitter signals interfere with the physiological/detector signals, potentially leading to erroneous physiological patient information, similar to but for different reasons a shifted or dislodged sensor.
- a low noise patient cable according to the present disclosure advantageously balances reduction of stiffness and size against the competing goal of reducing crosstalk.
- Various embodiments described herein disclose a cable that is relatively thin and flexible, yet is still able to mitigate crosstalk.
- One embodiment includes the emitter wires twisted around the detector wires such that the angle between the two functionally different wires is within a range that creates a measurable difference in crosstalk. In an embodiment, the angle is about 90 degrees. In other embodiment, the angle ranges to either side of about 90 degrees where the reduction in crosstalk is measurable and advantageous in order to accommodate other design goals, such as, for example, flexibility, shielding, etc.
- the presently disclosed low noise cable advantageously reduces harmful crosstalk before considering additional gains that can be accomplished using different twist rates or heavy shielding.
- embodiments of the present disclosure include tinsel wires and Kevlar material.
- Such construction materials advantageously provide a cable structure that is relatively thin and flexible, yet strong. It is noteworthy that the Applicants recognize that use of increasingly smaller diameter cable is not necessarily the natural progression of innovation in medical cabling like the smaller is better concepts from semiconductor fabrication. In contrast to semiconductor fabrication, in patient cabling innovation, reducing the cable diameter most often increases the resistance through the thinner wires. Thus, as a cable diameter shrinks, the spectroscopic analysis devices become inoperable as signals cannot be effectively or even operably transmitted due to the increase cable properties such as resistance.
- Embodiments of the low noise cable described herein balance the issues of cable diameter, resistance, shielding, etc. to disclose a cable that is thin and flexible, yet still able to effectively communicate the desired signals.
- This thin and flexible cable structure that mitigates crosstalk advantageously increases accuracy and reliability.
- FIG. 2 illustrates a simplified perspective view of an embodiment of an uncoated tinsel cable 200 .
- Tinsel cables as used herein include their ordinary broad meaning understood by an artisan and, from the disclosure herein, include a non-conductive fiber 201 , such as, for example, aramid fiber, that is coated with a thin layer of twisted conductive material 203 .
- the conductive material 203 is a silver copper alloy.
- the non-conductive fiber 201 provides strength and flexibility, while the conductive material 203 allows transmission of electrical signals.
- the conductive layer 203 is made very thin such that flexes in the cable 200 do not cause fatigue.
- FIG. 3 illustrates a simplified perspective view of an embodiment of a coated tinsel cable 300 .
- the coated cable 300 includes the same or similar materials as the uncoated tinsel cable 200 , but includes a plastic outer coating 205 .
- the plastic outer coating 205 includes fluorinated ethylene propylene (FEP).
- FEP fluorinated ethylene propylene
- FIG. 4 illustrates a simplified embodiment of a cross sectional view of each end of a low noise cable 400 according to portions of the present disclosure.
- the cable 400 includes an outer non-conductive protective jacket 401 , an outer shield layer 403 , an outer core 405 , an inner shield 407 , an inner core 409 and fiber filler 411 .
- the outer non-conductive protective jacket 401 is made of flexible insulation. In an embodiment, the protective jacket 401 is UV resistant polyurethane and has a diameter of about 4.0 mm.
- the outer shield layer 403 is made of twisted uncoated tinsel cable.
- the outer core 405 is made of a single layer of twisted coated tinsel cable.
- the inner shield 407 is again made of twisted uncoated tinsel cable.
- the inner core 409 is also again made of twisted coated tinsel cable, but also includes fiber fill 411 to provide some structure to the inner core and to provide tensile strength to help prevent the cable from tearing apart.
- the fiber fill is made of Kevlar to provide added strength.
- the fiber fill is made of aramid fiber.
- the cable has six fiber fill strands 411 .
- more or fewer wires could be used depending on the application of the cable and the number of transmission paths needed.
- the various wires in the inner and outer cores 405 and 409 can have different colors of insulation for easy identification.
- FIG. 5 illustrates the manner in which, in embodiments disclosed herein, wires in an inner core are twisted in an opposing fashion relative to wires in an outer core.
- FIG. 5 shows a simplified top-down view of a cable 500 , which includes inner wires 502 in an inner core twisted about the central axis of the cable 500 in a helical fashion.
- the cable 500 also includes outer wires 504 in an outer core, which are also twisted about the central axis of the cable 500 in a helical fashion but in an opposing rotational direction from the inner wires 502 .
- the angle ⁇ shown in FIG. 5 indicates the angle between the outer wires 504 and the inner wires 502 . Interference and crosstalk between the outer wires 504 and the inner wires 502 are reduced as the angle ⁇ approaches 90 degrees from either direction.
- the inner core is twisted clockwise and the outer core is twisted counter clockwise.
- This arrangement causes the outer core cables to be at about an angle of greater than 90 degrees to inner core cables, assisting in reducing crosstalk.
- the angle is between about 60 and about 120 degrees.
- the angle is between about 60 and about 90 degrees, and in a further embodiment, the angle is about 90 degrees.
- the angle is about 60 degrees.
- the inner core is used to transmit the relatively low voltage detector signals back to the monitor and the outer core is used to transmit the relatively high voltage emitter drive signals.
- the emitter wires are the inner core wires and the detector wires are the outer core wires.
- FIG. 6 illustrates another embodiment of a low noise sensor cable.
- tinsel cables are used in conjunction with standard wires, such as copper wires.
- the inner core 609 includes a set of triple twisted tinsel wires 641 , four sets of twisted pair tinsel wires 639 and three standard detector wires 643 .
- the inner core 609 of the FIG. 6 embodiment includes a fiber fill strand 411 to enhance the structure and tensile strength of the cable.
- An inner shield layer 607 separates the inner core wires from the outer core wires.
- An outer shield layer 603 surrounds the outer core 605 .
- a jacket 601 is disposed over the outer shield to form the cable.
- Embodiments described herein show enhanced resilience to mechanical stresses, such as kink resistance. Cables described herein and illustrated in FIG. 4 were tested to determine their resistance to electrical failure due to mechanical breakdown of the internal conductors and/or shielding after the cable is subjected to repeated attempted kinking.
- FIG. 7 illustrates the test setup.
- the setup includes a cable 700 secured into, for example, two mounting blocks 710 , 712 .
- a section of, for example, at least about twelve (12) inches of cable 700 is used for testing.
- two positions on the cable 700 approximately seven to eight inches apart are marked, and the cable 700 is grasped at those marks and twisted approximately 720 degrees. This twisting causes the cable to form a loop 740 as shown in FIG. 7 , and the cable 700 is then secured to the mounting blocks 710 , 712 at the marked positions.
- the mounting blocks 710 , 712 are attached to a track 718 .
- the first mounting block 710 is fixed to the track 718
- the second mounting block 712 is slidably attached to the track 718 .
- the second mounting block is also attached to a guide block 722 , which is in turn driven by a pneumatic cylinder 724 .
- the pneumatic cylinder 724 receives an air supply of approximately about 100 psi, which is regulated down to about 50 psi. This arrangement allows a tensile force of approximately 5-7 lbf. to be applied to the cable 700 .
- the pneumatic cylinder 724 pushes the guide block 722 and then pulls it back to the starting position, this constitutes one cycle of the test.
- FIG. 7 shows the testing apparatus when the pneumatic cylinder 724 is at its starting position. Because no tensile force is being applied to the cable 700 , the loop 740 is present.
- FIG. 8 shows the same testing apparatus when the pneumatic cylinder 724 is pushing on the guide block 722 , therefore applying a tensile force to the cable 700 . The effect of this tensile force is to attempt to produce a kink 742 in the cable 700 .
- the two ends 702 , 704 of the cable 700 are electrically connected to a break detect circuit test box 730 .
- the box 730 senses when a significant change of resistance occurs in the cable 700 , and when this occurs, the box 730 sends a signal to the pneumatic cylinder 724 to stop the testing.
- this test repeatedly subjects the cable 700 to kinking until an electrical failure occurs.
- the number of cycles the cable 700 can withstand before electrical failure is an indicator of its resilience to mechanical stresses.
- the cable tested is capable of withstanding more than 1,500 kinks with a high degree of reliability.
- the cables described herein are capable of withstanding, on average, more than 5,000 kinks. More particularly, the cables described herein are capable of withstanding, on average, more than 10,000 kinks. Still more particularly, the cables described herein are capable of withstanding, on average, more than 12,500 kinks. In an embodiment, the cables described herein are capable of withstanding in the range or 0 to 23,000 kinks.
- FIGS. 1A and 1B illustrate perspective views of physiological measurement systems utilizing a noninvasive optical sensor.
- the physiological measurement system 100 has a portable monitor 101 and docking station 103 that houses the portable monitor 101 .
- the portable monitor 101 has a display 105 to show physiological measurement data.
- the measurement data provides a readout of blood analytes, such as oxygen, carbon monoxide, methemoglobin, total hemoglobin, glucose, proteins, glucose, lipids, a percentage thereof (e.g., saturation), or other physiologically relevant patient characteristics.
- the portable monitor also has a speaker 107 to provide audible monitoring of physiological measurements, including, for example, the pulse rate.
- a user can operate the physiological measurement system and select between different available measurement data or other functionality for the user to manipulate, such as alarm settings, emitter settings, detector setting, and the like.
- a cable 111 docks into a monitor sensor port 113 and connects to a noninvasive optical sensor 115 that is fitted on a patient utilizing a clothespin-shaped enclosure with a contoured bed conforming generally to the shape of a finger.
- the cable 111 can be of various lengths to allow for separation between the portable monitor 101 and sensor 115 .
- the noninvasive optical sensor 115 has a set of emitters and detectors. The emitters serve as the source of optical radiation to irradiate patient tissue.
- the portable monitor 101 sends a drive signal to the emitters via the monitor sensor port 113 and through the cable 111 .
- the emitters produce optical radiation using one or more sources of optical radiation, such as LEDs, laser diodes, incandescent bulbs with appropriate frequency-selective filters, combination of the same, or the like.
- the radiation from the emitters is scattered and absorbed by the tissue such that some attenuated amount emerges and is detected by one or more detectors.
- the detectors produce a signal indicative of the intensity of the detected attenuated radiation and forward the signal via the cable through the monitor sensor port to the portable monitor for processing.
- FIG. 1B illustrates a perspective view of another portable physiological measurement system 150 utilizing a noninvasive optical sensor 151 .
- the system of FIG. 1B is similar to that of FIG. 1A described above except that the monitor 155 is a portable standalone device instead of being incorporated as a module or built-in portion of the physiological measurement system.
- the physiological measurement system 150 in FIG. 1B includes advanced functionality involving additional emitter and detectors in the sensor 151 . This allows the patient physiological measurement system 150 to determine more difficult to detect parameters such as, for example, glucose and total hemoglobin.
- the cable 153 is required to transmit more sensitive data that is easily corrupted by cross talk and other interference.
- the cabling described in the present disclosure is particularly suited to use in the patient monitor of FIG. 1B .
- the monitor 155 has a display 157 to show physiological measurement data and control buttons 159 that allow a user to operate the physiological measurement system 150 and select between different available measurement data or other functionality.
- code may include software, firmware, and/or microcode, and may refer to programs, routines, functions, classes, and/or objects.
- shared means that some or all code from multiple modules may be executed using a single (shared) processor. In addition, some or all code from multiple modules may be stored by a single (shared) memory.
- group means that some or all code from a single module may be executed using a group of processors. In addition, some or all code from a single module may be stored using a group of memories.
- the apparatuses and methods described herein may be implemented by one or more computer programs executed by one or more processors.
- the computer programs include processor-executable instructions that are stored on a non-transitory tangible computer readable medium.
- the computer programs may also include stored data.
- Non-limiting examples of the non-transitory tangible computer readable medium are nonvolatile memory, magnetic storage, and optical storage.
Abstract
A physiological measurement system can include a low noise patient cable that connects a monitor and a noninvasive optical sensor. The cable has a plurality of emitter wires configured to communicate a drive signal between the monitor and at least one emitter. The cable also has a plurality of detector wires configured to communicate a physiological signal between at least one detector responsive to the emitter and the monitor. The emitter and detector wires are orthogonally disposed so that crosstalk between the two functionally different wires is mitigated.
Description
- This application is a continuation of U.S. patent application Ser. No. 13/536,881, filed Jun. 28, 2012, pending, which claims a priority benefit under 35 U.S.C. §119(e) from U.S. Provisional Patent Application Ser. No. 61/502,740, filed on Jun. 29, 2011, titled “Low Noise Patient Cable” The '740 provisional application is incorporated by reference herein in its entirety.
- The present application is related to U.S. Publication No. 2003/0212312, filed on Dec. 19, 2002, entitled “Low Noise Patient Cable,” which is hereby incorporated by reference in its entirety.
- 1. Field of the Disclosure
- The present disclosure generally relates to patient monitoring devices and more specifically, embodiments of the present disclosure relate to cables connecting a monitor and a sensor of the patient monitoring device.
- 2. Description of the Related Art
- Physiological measurement systems using spectroscopic analysis are a widely accepted noninvasive procedure for measuring patient characteristics such as oxygen and glucose levels. Measuring these characteristics is important for patient wellness because for instance, an insufficient supply of oxygen can result in brain damage and death in a matter of minutes. Thus, early detection of low blood oxygen level is of crucial importance in the medical field, especially in critical care and surgical applications. Patient monitors commercially available from Masimo Corporation of Irvine Calif., USA, measure many physiological parameters including oxygen saturation, pulse rate, perfusion, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, overall wellness, respiration, combinations of the same and others.
- As shown in
FIGS. 1A and 1B , a physiological measurement system consists of amonitor 101, a noninvasiveoptical sensor 115 applied to a patient, and acable 111 connecting the sensor and the monitor. The system is controlled using input keys. Themonitor 101 may be a portable standalone device or may be incorporated as a module or built-in portion of a multiparameter patient monitoring system. The monitor displays measurements of various physiological patient characteristics on adisplay 105, which may include an oxygen saturation level, a pulse rate, and an audible indication of each pulse via aspeaker 107. In addition, themonitor 101 may display the patient's plethysmograph, which is a visual display of the patient's pulse contour and pulse rate, as well as a myriad of other measurements and calculated parameters. - To perform the above functions, the
monitor 101 energizes one or more emitters in thesensor 115 that irradiate tissue under observation, such as, for example, a finger, toe, foot, hand, ear, forehead or the like. The radiation from the emitters is scattered and absorbed by the tissue such that some attenuated amount emerges and is detected through one or more detectors located in thesensor 115. The detector(s) produces one or more signal(s) indicative of the intensity of the detected attenuated radiation and forward the signal(s) to thepatient monitor 101 for processing. Thesensor 115 that houses the emitters and the detectors can be disposable, reusable, or partially reusable and disposable. Reusable sensor may include a clothespin-shaped housing that includes a contoured bed conforming generally to the shape of a finger. The emitter and detector signals are transmitted over thecable 111 connecting the monitor and the sensor. - Depending on the nature of cables and the signals that are transmitted through cables, cables can be affected by a phenomenon known as crosstalk. Crosstalk occurs when energy from one signal interferes with another signal. Such interference can cause significant distortion in the transmission of information which can lead to incorrect measurements in physiological monitoring applications. As the
cable 111 often communicates high voltage emitter driving signals and low voltage sensitive detector signals, thecable 111 may unfortunately cause unwanted interference on the sensitive detector signals used to determine measurements of the physiological parameters. - The present disclosure provides a low noise tinsel cable arrangement particularly suited for transmitting communications between devices. In an embodiment, the cable is used to transmit electrical signals between a physiological sensor and a physiological monitor.
- In an embodiment, the cable has one or more emitter wires configured to communicate drive signals between a monitor and at least one emitter. The cable also has one or more detector wires configured to communicate a physiological signals between at least one detector and the monitor. The emitter wires transmit relatively high energy drive signals, while the detector wires transmit lower energy physiological signals. Due to the effect of crosstalk, the high energy drive/emitter signals can distort the lower energy physiological/detector signals.
- This is especially problematic because, unlike the known emitter drive signals generated by the monitor, the lower energy detector signal is an unknown signal. The unknown detector signal carries the important physiological patient information, such as, for example, signals responsive to absorption signals from the detector. Often, such absorption signals are lower energy signals and thus, often are more easily distorted. Thus, reducing interference with the detector signals improves system accuracy and reliability.
- Existing solutions to reduce crosstalk on the detector signals include use of different twist rates and heavy shielding in a cable. Different twist rates of wire pairs do not fully mitigate crosstalk because at certain points in the cable, the electromagnetic forces of the signals may still interact to cause interference. While a heavy shield between the wires could potentially reduce the majority of the crosstalk, this makes the cable stiff and thick. A bulky, cumbersome cable may pull the sensor away from an ideal position on the patient or pull it off altogether, leading to erroneous physiological patient information. Moreover, heavy shielding is also more susceptible to stress fractures from flexing of the cable, leading to a short lifespan. Thus, at least because of the foregoing, heavy shielding is at least somewhat of an impractical solution for communicating signals from a sensor to a spectroscopic analysis device.
- The present disclosure describes mitigating crosstalk by twisting the emitter wires about the central axis of the cable in an opposing rotational direction relative to the detector wires. Opposing twists advantageously seeks to create an angle between the two functionally different wires that approaches 90 degrees. At such an angle, crosstalk is reduced without requiring heavy shielding. One embodiment twists the detector wires in one direction down the center of the cable. The detector wires are insulated with an inner shield. Then the emitter wires are twisted in another direction around the inner shield such that the angle between the emitter wires and the detector wires is about 90 degrees. Put in other terms, the detector wires are twisted clockwise and the emitter wires are twisted counterclockwise, or vice versa. The emitter wires are insulated with an outer shield, and a jacket is disposed over the outer shield to form the cable.
- The disclosed opposing rotation of the wires mitigates crosstalk from the opposing rotation. This may be without or in addition to different twist rates or shielding. Opposing rotation in the cable structure may provide a more flexible cable, thereby not hindering sensor placement of the patient.
- In an embodiment, tinsel wires are used to form the cable. Tinsel wires are relatively thin and strong. Using tinsel wires allows the cable to be lighter and more flexible than equivalent all metal wires. While thinner wire is advantageous in some respects, reducing the cable diameter also increases the resistance through the wires. In an embodiment, the tinsel wires may also transmit the high energy drive signals. In such embodiments, the increasing resistance places some limitations on how small the cable diameter can be. The present disclosure accomplishes satisfactory signal transmission while simultaneously reducing the cable diameter.
-
FIG. 1A illustrates a perspective view of a physiological measurement system utilizing a noninvasive optical sensor. -
FIG. 1B illustrates a perspective view of a portable physiological measurement system utilizing a noninvasive optical sensor. -
FIG. 2 illustrates a perspective view of an embodiment of an uncoated tinsel cable. -
FIG. 3 illustrates a perspective view of an embodiment of a coated tinsel cable. -
FIG. 4 illustrates a cross sectional view of an embodiment of a low noise patient cable. -
FIG. 5 illustrates a top-down view of an embodiment of the cable ofFIG. 4 . -
FIG. 6 illustrates a cross sectional view of an embodiment of a low noise patient cable. -
FIG. 7 illustrates a block diagram of a simplified embodiment of a kink testing apparatus for a cable. -
FIG. 8 illustrates the testing apparatus ofFIG. 7 with the cable in a stretched position. - As shown in
FIGS. 1A and 1B (described in more detail below), aphysiological measurement systems 100 includes amonitor 101, acable 111, and asensor 115. Thesensor 115 can be any type of physiological sensor. Illustrated inFIGS. 1A and 1B are embodiments of noninvasive optical sensors. In the case of noninvasive optical sensors, themonitor 101 sends drive signals to one or more emitters in thesensor 115 via thecable 111. The emitters irradiate tissue under observation. One or more detectors in thesensor 115 detect the radiation leaving the tissue and send a signal back to the monitor via the cable responsive to the attenuation. This sequence produces more accurate results when the noninvasiveoptical sensor 115 remains substantially fixed with respect to the tissue of the patient. In the embodiment where thesensor 115 comprises a reusable sensor, thesensor 115 is often held in place by only the spring action of a clothespin-shaped housing. When a cable is stiff or bulky, as a patient moves to, for example, reposition themselves, the torque from the stiff or heavy cable may be more than the tension provided by the spring, thus even slightly shifting the optical components with respect to the measurement site on the tissue. A shifted or dislodged sensor could lead to erroneous physiological patient information. - As discussed in the foregoing, a stiff or bulky cable may be the result of utilizing heavy shielding to reduce damaging crosstalk. Crosstalk occurs when the drive/emitter signals interfere with the physiological/detector signals, potentially leading to erroneous physiological patient information, similar to but for different reasons a shifted or dislodged sensor. Thus, a low noise patient cable according to the present disclosure advantageously balances reduction of stiffness and size against the competing goal of reducing crosstalk.
- Various embodiments described herein disclose a cable that is relatively thin and flexible, yet is still able to mitigate crosstalk. One embodiment includes the emitter wires twisted around the detector wires such that the angle between the two functionally different wires is within a range that creates a measurable difference in crosstalk. In an embodiment, the angle is about 90 degrees. In other embodiment, the angle ranges to either side of about 90 degrees where the reduction in crosstalk is measurable and advantageous in order to accommodate other design goals, such as, for example, flexibility, shielding, etc.
- By controlling the angle between the differing cables, the presently disclosed low noise cable advantageously reduces harmful crosstalk before considering additional gains that can be accomplished using different twist rates or heavy shielding.
- Additionally, embodiments of the present disclosure include tinsel wires and Kevlar material. Such construction materials advantageously provide a cable structure that is relatively thin and flexible, yet strong. It is noteworthy that the Applicants recognize that use of increasingly smaller diameter cable is not necessarily the natural progression of innovation in medical cabling like the smaller is better concepts from semiconductor fabrication. In contrast to semiconductor fabrication, in patient cabling innovation, reducing the cable diameter most often increases the resistance through the thinner wires. Thus, as a cable diameter shrinks, the spectroscopic analysis devices become inoperable as signals cannot be effectively or even operably transmitted due to the increase cable properties such as resistance.
- Embodiments of the low noise cable described herein balance the issues of cable diameter, resistance, shielding, etc. to disclose a cable that is thin and flexible, yet still able to effectively communicate the desired signals. This thin and flexible cable structure that mitigates crosstalk advantageously increases accuracy and reliability.
-
FIG. 2 illustrates a simplified perspective view of an embodiment of anuncoated tinsel cable 200. Tinsel cables as used herein include their ordinary broad meaning understood by an artisan and, from the disclosure herein, include anon-conductive fiber 201, such as, for example, aramid fiber, that is coated with a thin layer of twistedconductive material 203. In an embodiment, theconductive material 203 is a silver copper alloy. Thenon-conductive fiber 201 provides strength and flexibility, while theconductive material 203 allows transmission of electrical signals. Theconductive layer 203 is made very thin such that flexes in thecable 200 do not cause fatigue. -
FIG. 3 illustrates a simplified perspective view of an embodiment of acoated tinsel cable 300. Thecoated cable 300 includes the same or similar materials as theuncoated tinsel cable 200, but includes a plasticouter coating 205. In an embodiment, the plasticouter coating 205 includes fluorinated ethylene propylene (FEP). An artisan will recognize from the disclosure herein that other constructions seeking to elevate associated advantages may also be used. -
FIG. 4 illustrates a simplified embodiment of a cross sectional view of each end of alow noise cable 400 according to portions of the present disclosure. Thecable 400 includes an outer non-conductiveprotective jacket 401, anouter shield layer 403, anouter core 405, aninner shield 407, aninner core 409 andfiber filler 411. The outer non-conductiveprotective jacket 401 is made of flexible insulation. In an embodiment, theprotective jacket 401 is UV resistant polyurethane and has a diameter of about 4.0 mm. Theouter shield layer 403 is made of twisted uncoated tinsel cable. Theouter core 405 is made of a single layer of twisted coated tinsel cable. Theinner shield 407 is again made of twisted uncoated tinsel cable. Theinner core 409 is also again made of twisted coated tinsel cable, but also includes fiber fill 411 to provide some structure to the inner core and to provide tensile strength to help prevent the cable from tearing apart. In an embodiment, the fiber fill is made of Kevlar to provide added strength. In an embodiment, the fiber fill is made of aramid fiber. In an embodiment, as illustrated inFIG. 4 , the cable has sixfiber fill strands 411. - In an embodiment, as illustrated in
FIG. 4 , there are fifteenouter core wires 405 and fifteeninner core wires 409. In other embodiments, more or fewer wires could be used depending on the application of the cable and the number of transmission paths needed. The various wires in the inner andouter cores - In order to minimize crosstalk, the
inner core 409 and theouter core 405 are twisted in opposing rotational directions.FIG. 5 illustrates the manner in which, in embodiments disclosed herein, wires in an inner core are twisted in an opposing fashion relative to wires in an outer core.FIG. 5 shows a simplified top-down view of acable 500, which includesinner wires 502 in an inner core twisted about the central axis of thecable 500 in a helical fashion. Thecable 500 also includesouter wires 504 in an outer core, which are also twisted about the central axis of thecable 500 in a helical fashion but in an opposing rotational direction from theinner wires 502. The angle θ shown inFIG. 5 indicates the angle between theouter wires 504 and theinner wires 502. Interference and crosstalk between theouter wires 504 and theinner wires 502 are reduced as the angle θ approaches 90 degrees from either direction. - For example, in one embodiment, the inner core is twisted clockwise and the outer core is twisted counter clockwise. This arrangement causes the outer core cables to be at about an angle of greater than 90 degrees to inner core cables, assisting in reducing crosstalk. In an embodiment, the angle is between about 60 and about 120 degrees. In another embodiment, the angle is between about 60 and about 90 degrees, and in a further embodiment, the angle is about 90 degrees. In still another embodiment, the angle is about 60 degrees.
- In an embodiment, the inner core is used to transmit the relatively low voltage detector signals back to the monitor and the outer core is used to transmit the relatively high voltage emitter drive signals. In an embodiment, the emitter wires are the inner core wires and the detector wires are the outer core wires.
-
FIG. 6 illustrates another embodiment of a low noise sensor cable. In this embodiment, tinsel cables are used in conjunction with standard wires, such as copper wires. In theouter core 605, there are four sets of threetinsel wires 635 and four sets of twostandard wires 637 that can be any standard conducting wire such as copper. Theinner core 609 includes a set of tripletwisted tinsel wires 641, four sets of twistedpair tinsel wires 639 and threestandard detector wires 643. As in the embodiment ofFIG. 4 , theinner core 609 of theFIG. 6 embodiment includes afiber fill strand 411 to enhance the structure and tensile strength of the cable. Aninner shield layer 607 separates the inner core wires from the outer core wires. Anouter shield layer 603 surrounds theouter core 605. Ajacket 601 is disposed over the outer shield to form the cable. - Embodiments described herein show enhanced resilience to mechanical stresses, such as kink resistance. Cables described herein and illustrated in
FIG. 4 were tested to determine their resistance to electrical failure due to mechanical breakdown of the internal conductors and/or shielding after the cable is subjected to repeated attempted kinking.FIG. 7 illustrates the test setup. The setup includes acable 700 secured into, for example, two mountingblocks cable 700 is used for testing. Before thecable 700 is secured to the mountingblocks cable 700 approximately seven to eight inches apart are marked, and thecable 700 is grasped at those marks and twisted approximately 720 degrees. This twisting causes the cable to form aloop 740 as shown inFIG. 7 , and thecable 700 is then secured to the mountingblocks - The mounting blocks 710, 712 are attached to a
track 718. Thefirst mounting block 710 is fixed to thetrack 718, and thesecond mounting block 712 is slidably attached to thetrack 718. The second mounting block is also attached to aguide block 722, which is in turn driven by apneumatic cylinder 724. Thepneumatic cylinder 724 receives an air supply of approximately about 100 psi, which is regulated down to about 50 psi. This arrangement allows a tensile force of approximately 5-7 lbf. to be applied to thecable 700. When thepneumatic cylinder 724 pushes theguide block 722 and then pulls it back to the starting position, this constitutes one cycle of the test. -
FIG. 7 shows the testing apparatus when thepneumatic cylinder 724 is at its starting position. Because no tensile force is being applied to thecable 700, theloop 740 is present.FIG. 8 shows the same testing apparatus when thepneumatic cylinder 724 is pushing on theguide block 722, therefore applying a tensile force to thecable 700. The effect of this tensile force is to attempt to produce akink 742 in thecable 700. - The two ends 702, 704 of the
cable 700 are electrically connected to a break detectcircuit test box 730. Thebox 730 senses when a significant change of resistance occurs in thecable 700, and when this occurs, thebox 730 sends a signal to thepneumatic cylinder 724 to stop the testing. Thus, this test repeatedly subjects thecable 700 to kinking until an electrical failure occurs. The number of cycles thecable 700 can withstand before electrical failure is an indicator of its resilience to mechanical stresses. - Twelve cable samples were subjected to this test. The results of the testing are shown below:
-
Sample Cycles to Failure 1 13,820 2 6,831 3 12,053 4 9,781 5 8,493 6 6,808 7 9,232 8 23,781 9 18,842 10 15,205 11 15,248 12 17,395 - As the table shows, the smallest number of cycles producing an electrical failure for the twelve samples tested was 6,808 cycles and the largest was number of cycles was 23,781. The mean cycles-to-failure was 13,124 and the median was 12,937. These results demonstrate that the cable described herein exhibit enhanced resilience to mechanical stress. Cables described herein are capable of withstanding more than 1,500 kinks with a high degree of reliability. Reliability can be measured using a Weibull Distribution Model. Applying that model with a shape parameter of Beta=1.7, in order for the cable to reliably withstand 1,500 kinks, none of the twelve samples tested should have a failure after 6,583 kink cycles. Because the smallest number of cycles producing an electrical failure for the twelve samples tested was 6,808 cycles, the cable tested is capable of withstanding more than 1,500 kinks with a high degree of reliability. The cables described herein are capable of withstanding, on average, more than 5,000 kinks. More particularly, the cables described herein are capable of withstanding, on average, more than 10,000 kinks. Still more particularly, the cables described herein are capable of withstanding, on average, more than 12,500 kinks. In an embodiment, the cables described herein are capable of withstanding in the range or 0 to 23,000 kinks.
-
FIGS. 1A and 1B illustrate perspective views of physiological measurement systems utilizing a noninvasive optical sensor. Referring specifically toFIG. 1A , thephysiological measurement system 100 has aportable monitor 101 anddocking station 103 that houses theportable monitor 101. Theportable monitor 101 has adisplay 105 to show physiological measurement data. The measurement data provides a readout of blood analytes, such as oxygen, carbon monoxide, methemoglobin, total hemoglobin, glucose, proteins, glucose, lipids, a percentage thereof (e.g., saturation), or other physiologically relevant patient characteristics. The portable monitor also has aspeaker 107 to provide audible monitoring of physiological measurements, including, for example, the pulse rate. Utilizing control buttons, a user can operate the physiological measurement system and select between different available measurement data or other functionality for the user to manipulate, such as alarm settings, emitter settings, detector setting, and the like. - A
cable 111 docks into amonitor sensor port 113 and connects to a noninvasiveoptical sensor 115 that is fitted on a patient utilizing a clothespin-shaped enclosure with a contoured bed conforming generally to the shape of a finger. Thecable 111 can be of various lengths to allow for separation between theportable monitor 101 andsensor 115. The noninvasiveoptical sensor 115 has a set of emitters and detectors. The emitters serve as the source of optical radiation to irradiate patient tissue. Theportable monitor 101 sends a drive signal to the emitters via themonitor sensor port 113 and through thecable 111. The emitters produce optical radiation using one or more sources of optical radiation, such as LEDs, laser diodes, incandescent bulbs with appropriate frequency-selective filters, combination of the same, or the like. The radiation from the emitters is scattered and absorbed by the tissue such that some attenuated amount emerges and is detected by one or more detectors. The detectors produce a signal indicative of the intensity of the detected attenuated radiation and forward the signal via the cable through the monitor sensor port to the portable monitor for processing. -
FIG. 1B illustrates a perspective view of another portablephysiological measurement system 150 utilizing a noninvasiveoptical sensor 151. The system ofFIG. 1B is similar to that ofFIG. 1A described above except that themonitor 155 is a portable standalone device instead of being incorporated as a module or built-in portion of the physiological measurement system. Moreover, thephysiological measurement system 150 inFIG. 1B includes advanced functionality involving additional emitter and detectors in thesensor 151. This allows the patientphysiological measurement system 150 to determine more difficult to detect parameters such as, for example, glucose and total hemoglobin. Moreover, thecable 153 is required to transmit more sensitive data that is easily corrupted by cross talk and other interference. As a result, the cabling described in the present disclosure is particularly suited to use in the patient monitor ofFIG. 1B . Themonitor 155 has adisplay 157 to show physiological measurement data andcontrol buttons 159 that allow a user to operate thephysiological measurement system 150 and select between different available measurement data or other functionality. - The term code, as used above, may include software, firmware, and/or microcode, and may refer to programs, routines, functions, classes, and/or objects. The term shared, as used above, means that some or all code from multiple modules may be executed using a single (shared) processor. In addition, some or all code from multiple modules may be stored by a single (shared) memory. The term group, as used above, means that some or all code from a single module may be executed using a group of processors. In addition, some or all code from a single module may be stored using a group of memories.
- The apparatuses and methods described herein may be implemented by one or more computer programs executed by one or more processors. The computer programs include processor-executable instructions that are stored on a non-transitory tangible computer readable medium. The computer programs may also include stored data. Non-limiting examples of the non-transitory tangible computer readable medium are nonvolatile memory, magnetic storage, and optical storage.
- Although the foregoing invention has been described in terms of certain preferred embodiments, other embodiments will be apparent to those of ordinary skill in the art from the disclosure herein. For example, additional or alternative materials may be used to enhance the low noise cable for the known properties of the additional or alternative materials without detracting from the novelty of the present disclosure. Moreover, different or additional testing apparatuses than those of
FIGS. 7 and 8 may provide useful insight into the flexibility and/or noise reduction of the present disclosure. Additionally, other combinations, omissions, substitutions and modifications will be apparent to the skilled artisan in view of the disclosure herein. Accordingly, the present disclosure is not intended to be limited by the reaction of the preferred embodiments, but is to be defined by reference to the appended claims. - Additionally, all publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application was specifically and individually indicated to be incorporated by reference.
Claims (21)
1. A low noise patient cable comprising:
a plurality of detector wires configured to communicate a physiological signal between a detector, which is responsive to energy received from an emitter, and a monitor;
a shield disposed over the plurality of detector wires;
a plurality of emitter wires configured to communicate a drive signal between the monitor and at least one emitter, wherein the plurality of emitter wires are twisted in an opposing rotational direction relative to the plurality of detector wires; and
a jacket comprising the plurality of detector wires, the shield, and the plurality of emitter wires, wherein a thickness of the shield is less than or equal to 4 mm.
2. The low noise patient cable of claim 1 , wherein an angle between the plurality of emitter wires and the plurality of detector wires is between about 60 degrees and about 90 degrees.
3. The low noise patient cable of claim 2 , wherein the plurality of detector wires are tinsel wires.
4. The low noise patient cable of claim 2 , further comprising a plurality filler wire.
5. The low noise patient cable of claim 4 , wherein the plurality filler wires comprise at least one of the following: kevlar wires and aramid wires.
6. The low noise patient cable of claim 2 , further comprising a second shield disposed over the plurality of emitter wires.
7. (canceled)
8. A method of making a cable, the method comprising:
twisting in a first direction a plurality of inner core wires;
using a shield over the plurality of inner core wires that does not limit flexibility of the cable;
twisting in a second direction a plurality of outer core wires around the shield, the second direction being opposite the first direction; and
disposing a jacket around the plurality of outer core wires.
9. The method of claim 8 , further comprising twisting a plurality of filler wires with the plurality of inner core wires.
10. The method of claim 8 , further comprising disposing a second shield around the plurality of outer core wires.
11. The method of claim 8 , further comprising twisting a plurality of filler wires with the plurality of inner core wires.
12. The method of claim 11 , wherein the filler wires are aramid.
13. The method of claim 11 , wherein the filler wires are Kevlar.
14. The method of claim 8 , wherein the inner and outer core wires are tinsel wires.
15. The method of claim 14 , wherein the tinsel wires are made from a silver copper alloy.
16. A low noise patient cable comprising:
a plurality of inner core wires twisted about a central axis of the cable in a first direction, the plurality of inner core wires being configured to communicate a first electrical signal;
a shield disposed over the plurality of inner core wires, the shield having a thickness that maintains flexibility of the plurality of inner core wires and the outer core wires, wherein the thickness is less than or equal to a diameter of a jacket;
a plurality of outer core wires twisted about the central axis in a second direction, the second direction being opposite the first direction, wherein the plurality of outer core wires are configured to communicate a second electrical signal, wherein the low noise patient cable does not electrically fail after being kinked more than 1,000 times.
17. The low noise patient cable of claim 16 , wherein the plurality of inner core wires are tinsel wires.
18. The low noise patient cable of claim 17 , wherein the tinsel wires are a silver copper alloy.
19. The low noise patient cable of claim 16 , further comprising a plurality filler wires twisted with the inner core wires.
20. The low noise patient cable of claim 16 , further comprising a second shield disposed over the plurality of outer core wires.
21.-27. (canceled)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15/003,747 US20160284441A1 (en) | 2011-06-29 | 2016-01-21 | Low noise cable providing communication between electronic sensor components and patient monitor |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US201161502740P | 2011-06-29 | 2011-06-29 | |
US13/536,881 US9245668B1 (en) | 2011-06-29 | 2012-06-28 | Low noise cable providing communication between electronic sensor components and patient monitor |
US15/003,747 US20160284441A1 (en) | 2011-06-29 | 2016-01-21 | Low noise cable providing communication between electronic sensor components and patient monitor |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/536,881 Continuation US9245668B1 (en) | 2011-06-29 | 2012-06-28 | Low noise cable providing communication between electronic sensor components and patient monitor |
Publications (1)
Publication Number | Publication Date |
---|---|
US20160284441A1 true US20160284441A1 (en) | 2016-09-29 |
Family
ID=55086226
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/536,881 Active 2033-09-02 US9245668B1 (en) | 2011-06-29 | 2012-06-28 | Low noise cable providing communication between electronic sensor components and patient monitor |
US15/003,747 Abandoned US20160284441A1 (en) | 2011-06-29 | 2016-01-21 | Low noise cable providing communication between electronic sensor components and patient monitor |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/536,881 Active 2033-09-02 US9245668B1 (en) | 2011-06-29 | 2012-06-28 | Low noise cable providing communication between electronic sensor components and patient monitor |
Country Status (1)
Country | Link |
---|---|
US (2) | US9245668B1 (en) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20170014623A1 (en) * | 2012-04-19 | 2017-01-19 | Medtronic, Inc. | Paired medical lead bodies with braided conductive shields having different physical parameter values |
WO2023042040A1 (en) * | 2021-09-17 | 2023-03-23 | Know Labs, Inc. | Noise reduction in non-invasive radio frequency analyte sensors |
Families Citing this family (208)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999062399A1 (en) | 1998-06-03 | 1999-12-09 | Masimo Corporation | Stereo pulse oximeter |
US6463311B1 (en) | 1998-12-30 | 2002-10-08 | Masimo Corporation | Plethysmograph pulse recognition processor |
US6684090B2 (en) | 1999-01-07 | 2004-01-27 | Masimo Corporation | Pulse oximetry data confidence indicator |
DE60139128D1 (en) | 2000-08-18 | 2009-08-13 | Masimo Corp | PULSE OXIMETER WITH TWO OPERATING MODES |
US6850787B2 (en) | 2001-06-29 | 2005-02-01 | Masimo Laboratories, Inc. | Signal component processor |
US6697658B2 (en) | 2001-07-02 | 2004-02-24 | Masimo Corporation | Low power pulse oximeter |
US7355512B1 (en) | 2002-01-24 | 2008-04-08 | Masimo Corporation | Parallel alarm processor |
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
US6920345B2 (en) | 2003-01-24 | 2005-07-19 | Masimo Corporation | Optical sensor including disposable and reusable elements |
US7003338B2 (en) | 2003-07-08 | 2006-02-21 | Masimo Corporation | Method and apparatus for reducing coupling between signals |
US7500950B2 (en) | 2003-07-25 | 2009-03-10 | Masimo Corporation | Multipurpose sensor port |
US7483729B2 (en) | 2003-11-05 | 2009-01-27 | Masimo Corporation | Pulse oximeter access apparatus and method |
EP1722676B1 (en) | 2004-03-08 | 2012-12-19 | Masimo Corporation | Physiological parameter system |
US7761127B2 (en) | 2005-03-01 | 2010-07-20 | Masimo Laboratories, Inc. | Multiple wavelength sensor substrate |
CA2604653A1 (en) | 2005-04-13 | 2006-10-19 | Glucolight Corporation | Method for data reduction and calibration of an oct-based blood glucose monitor |
US7962188B2 (en) | 2005-10-14 | 2011-06-14 | Masimo Corporation | Robust alarm system |
US8182443B1 (en) | 2006-01-17 | 2012-05-22 | Masimo Corporation | Drug administration controller |
US8219172B2 (en) | 2006-03-17 | 2012-07-10 | Glt Acquisition Corp. | System and method for creating a stable optical interface |
US7941199B2 (en) | 2006-05-15 | 2011-05-10 | Masimo Laboratories, Inc. | Sepsis monitor |
US10188348B2 (en) | 2006-06-05 | 2019-01-29 | Masimo Corporation | Parameter upgrade system |
US8457707B2 (en) | 2006-09-20 | 2013-06-04 | Masimo Corporation | Congenital heart disease monitor |
US8840549B2 (en) | 2006-09-22 | 2014-09-23 | Masimo Corporation | Modular patient monitor |
US9861305B1 (en) | 2006-10-12 | 2018-01-09 | Masimo Corporation | Method and apparatus for calibration to reduce coupling between signals in a measurement system |
US9192329B2 (en) | 2006-10-12 | 2015-11-24 | Masimo Corporation | Variable mode pulse indicator |
US7880626B2 (en) | 2006-10-12 | 2011-02-01 | Masimo Corporation | System and method for monitoring the life of a physiological sensor |
US8255026B1 (en) | 2006-10-12 | 2012-08-28 | Masimo Corporation, Inc. | Patient monitor capable of monitoring the quality of attached probes and accessories |
US8280473B2 (en) | 2006-10-12 | 2012-10-02 | Masino Corporation, Inc. | Perfusion index smoother |
US8265723B1 (en) | 2006-10-12 | 2012-09-11 | Cercacor Laboratories, Inc. | Oximeter probe off indicator defining probe off space |
US8600467B2 (en) | 2006-11-29 | 2013-12-03 | Cercacor Laboratories, Inc. | Optical sensor including disposable and reusable elements |
EP2096994B1 (en) | 2006-12-09 | 2018-10-03 | Masimo Corporation | Plethysmograph variability determination |
US8852094B2 (en) | 2006-12-22 | 2014-10-07 | Masimo Corporation | Physiological parameter system |
US8652060B2 (en) | 2007-01-20 | 2014-02-18 | Masimo Corporation | Perfusion trend indicator |
US8374665B2 (en) | 2007-04-21 | 2013-02-12 | Cercacor Laboratories, Inc. | Tissue profile wellness monitor |
US8768423B2 (en) | 2008-03-04 | 2014-07-01 | Glt Acquisition Corp. | Multispot monitoring for use in optical coherence tomography |
WO2009134724A1 (en) | 2008-05-02 | 2009-11-05 | Masimo Corporation | Monitor configuration system |
US9107625B2 (en) | 2008-05-05 | 2015-08-18 | Masimo Corporation | Pulse oximetry system with electrical decoupling circuitry |
US20100004518A1 (en) | 2008-07-03 | 2010-01-07 | Masimo Laboratories, Inc. | Heat sink for noninvasive medical sensor |
US8203438B2 (en) | 2008-07-29 | 2012-06-19 | Masimo Corporation | Alarm suspend system |
US8630691B2 (en) | 2008-08-04 | 2014-01-14 | Cercacor Laboratories, Inc. | Multi-stream sensor front ends for noninvasive measurement of blood constituents |
SE532941C2 (en) | 2008-09-15 | 2010-05-18 | Phasein Ab | Gas sampling line for breathing gases |
US8771204B2 (en) | 2008-12-30 | 2014-07-08 | Masimo Corporation | Acoustic sensor assembly |
US8588880B2 (en) | 2009-02-16 | 2013-11-19 | Masimo Corporation | Ear sensor |
US9323894B2 (en) | 2011-08-19 | 2016-04-26 | Masimo Corporation | Health care sanitation monitoring system |
US9218454B2 (en) | 2009-03-04 | 2015-12-22 | Masimo Corporation | Medical monitoring system |
US10032002B2 (en) | 2009-03-04 | 2018-07-24 | Masimo Corporation | Medical monitoring system |
US10007758B2 (en) | 2009-03-04 | 2018-06-26 | Masimo Corporation | Medical monitoring system |
US8388353B2 (en) | 2009-03-11 | 2013-03-05 | Cercacor Laboratories, Inc. | Magnetic connector |
WO2010135373A1 (en) | 2009-05-19 | 2010-11-25 | Masimo Corporation | Disposable components for reusable physiological sensor |
US8571619B2 (en) | 2009-05-20 | 2013-10-29 | Masimo Corporation | Hemoglobin display and patient treatment |
US20110208015A1 (en) | 2009-07-20 | 2011-08-25 | Masimo Corporation | Wireless patient monitoring system |
US8473020B2 (en) | 2009-07-29 | 2013-06-25 | Cercacor Laboratories, Inc. | Non-invasive physiological sensor cover |
US8688183B2 (en) | 2009-09-03 | 2014-04-01 | Ceracor Laboratories, Inc. | Emitter driver for noninvasive patient monitor |
US9579039B2 (en) | 2011-01-10 | 2017-02-28 | Masimo Corporation | Non-invasive intravascular volume index monitor |
US20110137297A1 (en) | 2009-09-17 | 2011-06-09 | Kiani Massi Joe E | Pharmacological management system |
US20110082711A1 (en) | 2009-10-06 | 2011-04-07 | Masimo Laboratories, Inc. | Personal digital assistant or organizer for monitoring glucose levels |
US10463340B2 (en) | 2009-10-15 | 2019-11-05 | Masimo Corporation | Acoustic respiratory monitoring systems and methods |
WO2011047216A2 (en) | 2009-10-15 | 2011-04-21 | Masimo Corporation | Physiological acoustic monitoring system |
US8790268B2 (en) | 2009-10-15 | 2014-07-29 | Masimo Corporation | Bidirectional physiological information display |
EP2488106B1 (en) | 2009-10-15 | 2020-07-08 | Masimo Corporation | Acoustic respiratory monitoring sensor having multiple sensing elements |
US9066680B1 (en) | 2009-10-15 | 2015-06-30 | Masimo Corporation | System for determining confidence in respiratory rate measurements |
US9848800B1 (en) | 2009-10-16 | 2017-12-26 | Masimo Corporation | Respiratory pause detector |
US9839381B1 (en) | 2009-11-24 | 2017-12-12 | Cercacor Laboratories, Inc. | Physiological measurement system with automatic wavelength adjustment |
DE112010004682T5 (en) | 2009-12-04 | 2013-03-28 | Masimo Corporation | Calibration for multi-level physiological monitors |
US9153112B1 (en) | 2009-12-21 | 2015-10-06 | Masimo Corporation | Modular patient monitor |
DE112011100282T5 (en) | 2010-01-19 | 2012-11-29 | Masimo Corporation | Wellness assessment system |
DE112011100761T5 (en) | 2010-03-01 | 2013-01-03 | Masimo Corporation | Adaptive alarm system |
WO2011112524A1 (en) | 2010-03-08 | 2011-09-15 | Masimo Corporation | Reprocessing of a physiological sensor |
US9307928B1 (en) | 2010-03-30 | 2016-04-12 | Masimo Corporation | Plethysmographic respiration processor |
US9138180B1 (en) | 2010-05-03 | 2015-09-22 | Masimo Corporation | Sensor adapter cable |
US8666468B1 (en) | 2010-05-06 | 2014-03-04 | Masimo Corporation | Patient monitor for determining microcirculation state |
US9408542B1 (en) | 2010-07-22 | 2016-08-09 | Masimo Corporation | Non-invasive blood pressure measurement system |
JP5710767B2 (en) | 2010-09-28 | 2015-04-30 | マシモ コーポレイション | Depth of consciousness monitor including oximeter |
US9775545B2 (en) | 2010-09-28 | 2017-10-03 | Masimo Corporation | Magnetic electrical connector for patient monitors |
US9211095B1 (en) | 2010-10-13 | 2015-12-15 | Masimo Corporation | Physiological measurement logic engine |
US20120226117A1 (en) | 2010-12-01 | 2012-09-06 | Lamego Marcelo M | Handheld processing device including medical applications for minimally and non invasive glucose measurements |
WO2012109671A1 (en) | 2011-02-13 | 2012-08-16 | Masimo Corporation | Medical characterization system |
US9066666B2 (en) | 2011-02-25 | 2015-06-30 | Cercacor Laboratories, Inc. | Patient monitor for monitoring microcirculation |
US9986919B2 (en) | 2011-06-21 | 2018-06-05 | Masimo Corporation | Patient monitoring system |
US9532722B2 (en) | 2011-06-21 | 2017-01-03 | Masimo Corporation | Patient monitoring system |
US11439329B2 (en) | 2011-07-13 | 2022-09-13 | Masimo Corporation | Multiple measurement mode in a physiological sensor |
US9782077B2 (en) | 2011-08-17 | 2017-10-10 | Masimo Corporation | Modulated physiological sensor |
EP3603502B1 (en) | 2011-10-13 | 2023-10-04 | Masimo Corporation | Physiological acoustic monitoring system |
WO2013056160A2 (en) | 2011-10-13 | 2013-04-18 | Masimo Corporation | Medical monitoring hub |
US9808188B1 (en) | 2011-10-13 | 2017-11-07 | Masimo Corporation | Robust fractional saturation determination |
US9943269B2 (en) | 2011-10-13 | 2018-04-17 | Masimo Corporation | System for displaying medical monitoring data |
US9778079B1 (en) | 2011-10-27 | 2017-10-03 | Masimo Corporation | Physiological monitor gauge panel |
US9392945B2 (en) | 2012-01-04 | 2016-07-19 | Masimo Corporation | Automated CCHD screening and detection |
US11172890B2 (en) | 2012-01-04 | 2021-11-16 | Masimo Corporation | Automated condition screening and detection |
US10149616B2 (en) | 2012-02-09 | 2018-12-11 | Masimo Corporation | Wireless patient monitoring device |
US9480435B2 (en) | 2012-02-09 | 2016-11-01 | Masimo Corporation | Configurable patient monitoring system |
US9195385B2 (en) | 2012-03-25 | 2015-11-24 | Masimo Corporation | Physiological monitor touchscreen interface |
JP6490577B2 (en) | 2012-04-17 | 2019-03-27 | マシモ・コーポレイション | How to operate a pulse oximeter device |
WO2013184965A1 (en) | 2012-06-07 | 2013-12-12 | Masimo Corporation | Depth of consciousness monitor |
US9697928B2 (en) | 2012-08-01 | 2017-07-04 | Masimo Corporation | Automated assembly sensor cable |
US10827961B1 (en) | 2012-08-29 | 2020-11-10 | Masimo Corporation | Physiological measurement calibration |
US9955937B2 (en) | 2012-09-20 | 2018-05-01 | Masimo Corporation | Acoustic patient sensor coupler |
US9877650B2 (en) | 2012-09-20 | 2018-01-30 | Masimo Corporation | Physiological monitor with mobile computing device connectivity |
US9749232B2 (en) | 2012-09-20 | 2017-08-29 | Masimo Corporation | Intelligent medical network edge router |
US9717458B2 (en) | 2012-10-20 | 2017-08-01 | Masimo Corporation | Magnetic-flap optical sensor |
US9560996B2 (en) | 2012-10-30 | 2017-02-07 | Masimo Corporation | Universal medical system |
US9787568B2 (en) | 2012-11-05 | 2017-10-10 | Cercacor Laboratories, Inc. | Physiological test credit method |
DE202012010854U1 (en) * | 2012-11-13 | 2012-11-28 | Ondal Medical Systems Gmbh | Coaxial cable for the electrical transmission of a high-frequency and / or high-speed data signal, rotary coupling with two such coaxial cables, and a holding device with at least one such rotary coupling |
US9750461B1 (en) | 2013-01-02 | 2017-09-05 | Masimo Corporation | Acoustic respiratory monitoring sensor with probe-off detection |
US9724025B1 (en) | 2013-01-16 | 2017-08-08 | Masimo Corporation | Active-pulse blood analysis system |
US9750442B2 (en) | 2013-03-09 | 2017-09-05 | Masimo Corporation | Physiological status monitor |
WO2014164139A1 (en) | 2013-03-13 | 2014-10-09 | Masimo Corporation | Systems and methods for monitoring a patient health network |
US10441181B1 (en) | 2013-03-13 | 2019-10-15 | Masimo Corporation | Acoustic pulse and respiration monitoring system |
US9936917B2 (en) | 2013-03-14 | 2018-04-10 | Masimo Laboratories, Inc. | Patient monitor placement indicator |
US9891079B2 (en) | 2013-07-17 | 2018-02-13 | Masimo Corporation | Pulser with double-bearing position encoder for non-invasive physiological monitoring |
WO2015020911A2 (en) | 2013-08-05 | 2015-02-12 | Cercacor Laboratories, Inc. | Blood pressure monitor with valve-chamber assembly |
WO2015038683A2 (en) | 2013-09-12 | 2015-03-19 | Cercacor Laboratories, Inc. | Medical device management system |
US10010276B2 (en) | 2013-10-07 | 2018-07-03 | Masimo Corporation | Regional oximetry user interface |
US11147518B1 (en) | 2013-10-07 | 2021-10-19 | Masimo Corporation | Regional oximetry signal processor |
US10828007B1 (en) | 2013-10-11 | 2020-11-10 | Masimo Corporation | Acoustic sensor with attachment portion |
US10832818B2 (en) | 2013-10-11 | 2020-11-10 | Masimo Corporation | Alarm notification system |
US9863996B2 (en) * | 2013-12-12 | 2018-01-09 | Carlos Gutierrez Martinez | Apparatus and process for testing and improving electrical and/or mechanical characteristics of an electrical connection |
US10279247B2 (en) | 2013-12-13 | 2019-05-07 | Masimo Corporation | Avatar-incentive healthcare therapy |
US11259745B2 (en) | 2014-01-28 | 2022-03-01 | Masimo Corporation | Autonomous drug delivery system |
US10086138B1 (en) | 2014-01-28 | 2018-10-02 | Masimo Corporation | Autonomous drug delivery system |
US10123729B2 (en) | 2014-06-13 | 2018-11-13 | Nanthealth, Inc. | Alarm fatigue management systems and methods |
US10231670B2 (en) | 2014-06-19 | 2019-03-19 | Masimo Corporation | Proximity sensor in pulse oximeter |
US10111591B2 (en) | 2014-08-26 | 2018-10-30 | Nanthealth, Inc. | Real-time monitoring systems and methods in a healthcare environment |
US10231657B2 (en) | 2014-09-04 | 2019-03-19 | Masimo Corporation | Total hemoglobin screening sensor |
US10383520B2 (en) | 2014-09-18 | 2019-08-20 | Masimo Semiconductor, Inc. | Enhanced visible near-infrared photodiode and non-invasive physiological sensor |
WO2016057553A1 (en) | 2014-10-07 | 2016-04-14 | Masimo Corporation | Modular physiological sensors |
KR102575058B1 (en) | 2015-01-23 | 2023-09-05 | 마시모 스웨덴 에이비 | Nasal/Oral Cannula Systems and Manufacturing |
US10568553B2 (en) | 2015-02-06 | 2020-02-25 | Masimo Corporation | Soft boot pulse oximetry sensor |
MX2017010045A (en) | 2015-02-06 | 2018-04-10 | Masimo Corp | Connector assembly with pogo pins for use with medical sensors. |
KR102609605B1 (en) | 2015-02-06 | 2023-12-05 | 마시모 코오퍼레이션 | Fold flex circuit for optical probes |
US10524738B2 (en) | 2015-05-04 | 2020-01-07 | Cercacor Laboratories, Inc. | Noninvasive sensor system with visual infographic display |
WO2016191307A1 (en) | 2015-05-22 | 2016-12-01 | Cercacor Laboratories, Inc. | Non-invasive optical physiological differential pathlength sensor |
US10448871B2 (en) | 2015-07-02 | 2019-10-22 | Masimo Corporation | Advanced pulse oximetry sensor |
EP3334334A1 (en) | 2015-08-11 | 2018-06-20 | Masimo Corporation | Medical monitoring analysis and replay including indicia responsive to light attenuated by body tissue |
AU2016315947B2 (en) | 2015-08-31 | 2021-02-18 | Masimo Corporation | Wireless patient monitoring systems and methods |
US11504066B1 (en) | 2015-09-04 | 2022-11-22 | Cercacor Laboratories, Inc. | Low-noise sensor system |
US11679579B2 (en) | 2015-12-17 | 2023-06-20 | Masimo Corporation | Varnish-coated release liner |
US10993662B2 (en) | 2016-03-04 | 2021-05-04 | Masimo Corporation | Nose sensor |
US10537285B2 (en) | 2016-03-04 | 2020-01-21 | Masimo Corporation | Nose sensor |
US11191484B2 (en) | 2016-04-29 | 2021-12-07 | Masimo Corporation | Optical sensor tape |
US10608817B2 (en) | 2016-07-06 | 2020-03-31 | Masimo Corporation | Secure and zero knowledge data sharing for cloud applications |
US10617302B2 (en) | 2016-07-07 | 2020-04-14 | Masimo Corporation | Wearable pulse oximeter and respiration monitor |
WO2018071715A1 (en) | 2016-10-13 | 2018-04-19 | Masimo Corporation | Systems and methods for patient fall detection |
US11504058B1 (en) | 2016-12-02 | 2022-11-22 | Masimo Corporation | Multi-site noninvasive measurement of a physiological parameter |
US10750984B2 (en) | 2016-12-22 | 2020-08-25 | Cercacor Laboratories, Inc. | Methods and devices for detecting intensity of light with translucent detector |
US10721785B2 (en) | 2017-01-18 | 2020-07-21 | Masimo Corporation | Patient-worn wireless physiological sensor with pairing functionality |
WO2018156648A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | Managing dynamic licenses for physiological parameters in a patient monitoring environment |
US10327713B2 (en) | 2017-02-24 | 2019-06-25 | Masimo Corporation | Modular multi-parameter patient monitoring device |
WO2018156809A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | Augmented reality system for displaying patient data |
WO2018156804A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | System for displaying medical monitoring data |
US11086609B2 (en) | 2017-02-24 | 2021-08-10 | Masimo Corporation | Medical monitoring hub |
US10388120B2 (en) | 2017-02-24 | 2019-08-20 | Masimo Corporation | Localized projection of audible noises in medical settings |
CN110891486A (en) | 2017-03-10 | 2020-03-17 | 梅西莫股份有限公司 | Pneumonia screening instrument |
WO2018194992A1 (en) | 2017-04-18 | 2018-10-25 | Masimo Corporation | Nose sensor |
US10918281B2 (en) | 2017-04-26 | 2021-02-16 | Masimo Corporation | Medical monitoring device having multiple configurations |
USD835285S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
EP3614909B1 (en) | 2017-04-28 | 2024-04-03 | Masimo Corporation | Spot check measurement system |
USD835284S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD835283S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD835282S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
WO2018208616A1 (en) | 2017-05-08 | 2018-11-15 | Masimo Corporation | System for pairing a medical system to a network controller by use of a dongle |
US11026604B2 (en) | 2017-07-13 | 2021-06-08 | Cercacor Laboratories, Inc. | Medical monitoring device for harmonizing physiological measurements |
USD906970S1 (en) | 2017-08-15 | 2021-01-05 | Masimo Corporation | Connector |
US10637181B2 (en) | 2017-08-15 | 2020-04-28 | Masimo Corporation | Water resistant connector for noninvasive patient monitor |
USD890708S1 (en) | 2017-08-15 | 2020-07-21 | Masimo Corporation | Connector |
EP4039177A1 (en) | 2017-10-19 | 2022-08-10 | Masimo Corporation | Display arrangement for medical monitoring system |
USD925597S1 (en) | 2017-10-31 | 2021-07-20 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
EP3703566B1 (en) | 2017-10-31 | 2023-07-26 | Masimo Corporation | System for displaying oxygen state indications |
US11766198B2 (en) | 2018-02-02 | 2023-09-26 | Cercacor Laboratories, Inc. | Limb-worn patient monitoring device |
WO2019204368A1 (en) | 2018-04-19 | 2019-10-24 | Masimo Corporation | Mobile patient alarm display |
WO2019209915A1 (en) | 2018-04-24 | 2019-10-31 | Cercacor Laboratories, Inc. | Easy insert finger sensor for transmission based spectroscopy sensor |
US11627919B2 (en) | 2018-06-06 | 2023-04-18 | Masimo Corporation | Opioid overdose monitoring |
US10779098B2 (en) | 2018-07-10 | 2020-09-15 | Masimo Corporation | Patient monitor alarm speaker analyzer |
US11872156B2 (en) | 2018-08-22 | 2024-01-16 | Masimo Corporation | Core body temperature measurement |
USD917550S1 (en) | 2018-10-11 | 2021-04-27 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
USD998630S1 (en) | 2018-10-11 | 2023-09-12 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
USD916135S1 (en) | 2018-10-11 | 2021-04-13 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
US11406286B2 (en) | 2018-10-11 | 2022-08-09 | Masimo Corporation | Patient monitoring device with improved user interface |
US11389093B2 (en) | 2018-10-11 | 2022-07-19 | Masimo Corporation | Low noise oximetry cable |
USD998631S1 (en) | 2018-10-11 | 2023-09-12 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
JP7128960B2 (en) | 2018-10-11 | 2022-08-31 | マシモ・コーポレイション | Patient connector assembly with vertical detent |
USD999246S1 (en) | 2018-10-11 | 2023-09-19 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
USD917564S1 (en) | 2018-10-11 | 2021-04-27 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
AU2019357721A1 (en) | 2018-10-12 | 2021-05-27 | Masimo Corporation | System for transmission of sensor data using dual communication protocol |
USD897098S1 (en) | 2018-10-12 | 2020-09-29 | Masimo Corporation | Card holder set |
US11464410B2 (en) | 2018-10-12 | 2022-10-11 | Masimo Corporation | Medical systems and methods |
US11684296B2 (en) | 2018-12-21 | 2023-06-27 | Cercacor Laboratories, Inc. | Noninvasive physiological sensor |
US11701043B2 (en) | 2019-04-17 | 2023-07-18 | Masimo Corporation | Blood pressure monitor attachment assembly |
USD985498S1 (en) | 2019-08-16 | 2023-05-09 | Masimo Corporation | Connector |
USD917704S1 (en) | 2019-08-16 | 2021-04-27 | Masimo Corporation | Patient monitor |
USD919094S1 (en) | 2019-08-16 | 2021-05-11 | Masimo Corporation | Blood pressure device |
USD921202S1 (en) | 2019-08-16 | 2021-06-01 | Masimo Corporation | Holder for a blood pressure device |
USD919100S1 (en) | 2019-08-16 | 2021-05-11 | Masimo Corporation | Holder for a patient monitor |
US11832940B2 (en) | 2019-08-27 | 2023-12-05 | Cercacor Laboratories, Inc. | Non-invasive medical monitoring device for blood analyte measurements |
USD927699S1 (en) | 2019-10-18 | 2021-08-10 | Masimo Corporation | Electrode pad |
KR20220083771A (en) | 2019-10-18 | 2022-06-20 | 마시모 코오퍼레이션 | Display layouts and interactive objects for patient monitoring |
CA3157995A1 (en) | 2019-10-25 | 2021-04-29 | Cercacor Laboratories, Inc. | Indicator compounds, devices comprising indicator compounds, and methods of making and using the same |
EP4104037A1 (en) | 2020-02-13 | 2022-12-21 | Masimo Corporation | System and method for monitoring clinical activities |
US11879960B2 (en) | 2020-02-13 | 2024-01-23 | Masimo Corporation | System and method for monitoring clinical activities |
US20210290177A1 (en) | 2020-03-20 | 2021-09-23 | Masimo Corporation | Wearable device for monitoring health status |
USD933232S1 (en) | 2020-05-11 | 2021-10-12 | Masimo Corporation | Blood pressure monitor |
USD979516S1 (en) | 2020-05-11 | 2023-02-28 | Masimo Corporation | Connector |
USD980091S1 (en) | 2020-07-27 | 2023-03-07 | Masimo Corporation | Wearable temperature measurement device |
USD974193S1 (en) | 2020-07-27 | 2023-01-03 | Masimo Corporation | Wearable temperature measurement device |
USD946598S1 (en) | 2020-09-30 | 2022-03-22 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
USD946597S1 (en) | 2020-09-30 | 2022-03-22 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
USD946596S1 (en) | 2020-09-30 | 2022-03-22 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
USD997365S1 (en) | 2021-06-24 | 2023-08-29 | Masimo Corporation | Physiological nose sensor |
USD1000975S1 (en) | 2021-09-22 | 2023-10-10 | Masimo Corporation | Wearable temperature measurement device |
Family Cites Families (302)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4280507A (en) * | 1979-06-27 | 1981-07-28 | Hewlett-Packard Company | Patient cable with distributed resistance protection in conductors |
US4461923A (en) * | 1981-03-23 | 1984-07-24 | Virginia Patent Development Corporation | Round shielded cable and modular connector therefor |
US5041187A (en) | 1988-04-29 | 1991-08-20 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and method of forming the same |
US5069213A (en) | 1988-04-29 | 1991-12-03 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and encoder |
US4964408A (en) | 1988-04-29 | 1990-10-23 | Thor Technology Corporation | Oximeter sensor assembly with integral cable |
US4960128A (en) | 1988-11-14 | 1990-10-02 | Paramed Technology Incorporated | Method and apparatus for continuously and non-invasively measuring the blood pressure of a patient |
US5163438A (en) | 1988-11-14 | 1992-11-17 | Paramed Technology Incorporated | Method and apparatus for continuously and noninvasively measuring the blood pressure of a patient |
GB9011887D0 (en) | 1990-05-26 | 1990-07-18 | Le Fit Ltd | Pulse responsive device |
US5319355A (en) | 1991-03-06 | 1994-06-07 | Russek Linda G | Alarm for patient monitor and life support equipment system |
ATE184716T1 (en) | 1991-03-07 | 1999-10-15 | Masimo Corp | DEVICE AND METHOD FOR SIGNAL PROCESSING |
US5490505A (en) | 1991-03-07 | 1996-02-13 | Masimo Corporation | Signal processing apparatus |
MX9702434A (en) | 1991-03-07 | 1998-05-31 | Masimo Corp | Signal processing apparatus. |
US5632272A (en) | 1991-03-07 | 1997-05-27 | Masimo Corporation | Signal processing apparatus |
US5645440A (en) | 1995-10-16 | 1997-07-08 | Masimo Corporation | Patient cable connector |
US5638818A (en) | 1991-03-21 | 1997-06-17 | Masimo Corporation | Low noise optical probe |
US6580086B1 (en) | 1999-08-26 | 2003-06-17 | Masimo Corporation | Shielded optical probe and method |
US6541756B2 (en) | 1991-03-21 | 2003-04-01 | Masimo Corporation | Shielded optical probe having an electrical connector |
US5995855A (en) | 1998-02-11 | 1999-11-30 | Masimo Corporation | Pulse oximetry sensor adapter |
US5377676A (en) | 1991-04-03 | 1995-01-03 | Cedars-Sinai Medical Center | Method for determining the biodistribution of substances using fluorescence spectroscopy |
AU667199B2 (en) | 1991-11-08 | 1996-03-14 | Physiometrix, Inc. | EEG headpiece with disposable electrodes and apparatus and system and method for use therewith |
DE9215099U1 (en) * | 1992-11-06 | 1992-12-17 | B. Braun Melsungen Ag, 3508 Melsungen, De | |
CA2140658C (en) | 1992-12-07 | 2001-07-24 | Jocelyn Durand | Electronic stethoscope |
US5341805A (en) | 1993-04-06 | 1994-08-30 | Cedars-Sinai Medical Center | Glucose fluorescence monitor and method |
US5494043A (en) | 1993-05-04 | 1996-02-27 | Vital Insite, Inc. | Arterial sensor |
USD353196S (en) | 1993-05-28 | 1994-12-06 | Gary Savage | Stethoscope head |
USD353195S (en) | 1993-05-28 | 1994-12-06 | Gary Savage | Electronic stethoscope housing |
US5337744A (en) | 1993-07-14 | 1994-08-16 | Masimo Corporation | Low noise finger cot probe |
US5452717A (en) | 1993-07-14 | 1995-09-26 | Masimo Corporation | Finger-cot probe |
US5456252A (en) | 1993-09-30 | 1995-10-10 | Cedars-Sinai Medical Center | Induced fluorescence spectroscopy blood perfusion and pH monitor and method |
US7376453B1 (en) | 1993-10-06 | 2008-05-20 | Masimo Corporation | Signal processing apparatus |
US5533511A (en) | 1994-01-05 | 1996-07-09 | Vital Insite, Incorporated | Apparatus and method for noninvasive blood pressure measurement |
USD359546S (en) | 1994-01-27 | 1995-06-20 | The Ratechnologies Inc. | Housing for a dental unit disinfecting device |
US5483022A (en) * | 1994-04-12 | 1996-01-09 | Ventritex, Inc. | Implantable conductor coil formed from cabled composite wire |
US6371921B1 (en) | 1994-04-15 | 2002-04-16 | Masimo Corporation | System and method of determining whether to recalibrate a blood pressure monitor |
US5590649A (en) | 1994-04-15 | 1997-01-07 | Vital Insite, Inc. | Apparatus and method for measuring an induced perturbation to determine blood pressure |
US5904654A (en) | 1995-10-20 | 1999-05-18 | Vital Insite, Inc. | Exciter-detector unit for measuring physiological parameters |
US5810734A (en) | 1994-04-15 | 1998-09-22 | Vital Insite, Inc. | Apparatus and method for measuring an induced perturbation to determine a physiological parameter |
US5785659A (en) | 1994-04-15 | 1998-07-28 | Vital Insite, Inc. | Automatically activated blood pressure measurement device |
US5791347A (en) | 1994-04-15 | 1998-08-11 | Vital Insite, Inc. | Motion insensitive pulse detector |
USD363120S (en) | 1994-04-21 | 1995-10-10 | Gary Savage | Stethoscope ear tip |
USD362063S (en) | 1994-04-21 | 1995-09-05 | Gary Savage | Stethoscope headset |
USD361840S (en) | 1994-04-21 | 1995-08-29 | Gary Savage | Stethoscope head |
US5561275A (en) | 1994-04-28 | 1996-10-01 | Delstar Services Informatiques (1993) Inc. | Headset for electronic stethoscope |
US5491299A (en) * | 1994-06-03 | 1996-02-13 | Siemens Medical Systems, Inc. | Flexible multi-parameter cable |
US8019400B2 (en) | 1994-10-07 | 2011-09-13 | Masimo Corporation | Signal processing apparatus |
EP1905352B1 (en) | 1994-10-07 | 2014-07-16 | Masimo Corporation | Signal processing method |
US5562002A (en) | 1995-02-03 | 1996-10-08 | Sensidyne Inc. | Positive displacement piston flow meter with damping assembly |
US5552565A (en) * | 1995-03-31 | 1996-09-03 | Hewlett-Packard Company | Multiconductor shielded transducer cable |
US6931268B1 (en) | 1995-06-07 | 2005-08-16 | Masimo Laboratories, Inc. | Active pulse blood constituent monitoring |
US5743262A (en) | 1995-06-07 | 1998-04-28 | Masimo Corporation | Blood glucose monitoring system |
US5638816A (en) | 1995-06-07 | 1997-06-17 | Masimo Corporation | Active pulse blood constituent monitoring |
US5758644A (en) | 1995-06-07 | 1998-06-02 | Masimo Corporation | Manual and automatic probe calibration |
US6517283B2 (en) | 2001-01-16 | 2003-02-11 | Donald Edward Coffey | Cascading chute drainage system |
US5760910A (en) | 1995-06-07 | 1998-06-02 | Masimo Corporation | Optical filter for spectroscopic measurement and method of producing the optical filter |
USD393830S (en) | 1995-10-16 | 1998-04-28 | Masimo Corporation | Patient cable connector |
US6232609B1 (en) | 1995-12-01 | 2001-05-15 | Cedars-Sinai Medical Center | Glucose monitoring apparatus and method using laser-induced emission spectroscopy |
FR2745117B1 (en) * | 1996-02-21 | 2000-10-13 | Whitaker Corp | FLEXIBLE AND FLEXIBLE CABLE WITH SPACED PROPELLERS |
US6030346A (en) * | 1996-02-21 | 2000-02-29 | The Whitaker Corporation | Ultrasound imaging probe assembly |
US6117083A (en) * | 1996-02-21 | 2000-09-12 | The Whitaker Corporation | Ultrasound imaging probe assembly |
US6253097B1 (en) | 1996-03-06 | 2001-06-26 | Datex-Ohmeda, Inc. | Noninvasive medical monitoring instrument using surface emitting laser devices |
US5824026A (en) * | 1996-06-12 | 1998-10-20 | The Spectranetics Corporation | Catheter for delivery of electric energy and a process for manufacturing same |
US5890929A (en) | 1996-06-19 | 1999-04-06 | Masimo Corporation | Shielded medical connector |
US6027452A (en) | 1996-06-26 | 2000-02-22 | Vital Insite, Inc. | Rapid non-invasive blood pressure measuring device |
US5760341A (en) * | 1996-09-10 | 1998-06-02 | Medtronic, Inc. | Conductor cable for biomedical lead |
SE9603318D0 (en) * | 1996-09-12 | 1996-09-12 | Pacesetter Ab | Electrode cable for electrical stimulation |
US5937950A (en) * | 1996-12-02 | 1999-08-17 | Medex, Inc. | Cable system for medical equipment |
US5796044A (en) * | 1997-02-10 | 1998-08-18 | Medtronic, Inc. | Coiled wire conductor insulation for biomedical lead |
JP3853899B2 (en) * | 1997-02-27 | 2006-12-06 | オリンパス株式会社 | Composite coaxial cable for electronic endoscope and electronic endoscope |
US6002952A (en) | 1997-04-14 | 1999-12-14 | Masimo Corporation | Signal processing apparatus and method |
US6229856B1 (en) | 1997-04-14 | 2001-05-08 | Masimo Corporation | Method and apparatus for demodulating signals in a pulse oximetry system |
US5919134A (en) | 1997-04-14 | 1999-07-06 | Masimo Corp. | Method and apparatus for demodulating signals in a pulse oximetry system |
US6124597A (en) | 1997-07-07 | 2000-09-26 | Cedars-Sinai Medical Center | Method and devices for laser induced fluorescence attenuation spectroscopy |
US6184521B1 (en) | 1998-01-06 | 2001-02-06 | Masimo Corporation | Photodiode detector with integrated noise shielding |
US6241683B1 (en) | 1998-02-20 | 2001-06-05 | INSTITUT DE RECHERCHES CLINIQUES DE MONTRéAL (IRCM) | Phonospirometry for non-invasive monitoring of respiration |
US6525386B1 (en) | 1998-03-10 | 2003-02-25 | Masimo Corporation | Non-protruding optoelectronic lens |
US5997343A (en) | 1998-03-19 | 1999-12-07 | Masimo Corporation | Patient cable sensor switch |
US6165005A (en) | 1998-03-19 | 2000-12-26 | Masimo Corporation | Patient cable sensor switch |
US6728560B2 (en) | 1998-04-06 | 2004-04-27 | The General Hospital Corporation | Non-invasive tissue glucose level monitoring |
US6505059B1 (en) | 1998-04-06 | 2003-01-07 | The General Hospital Corporation | Non-invasive tissue glucose level monitoring |
US6721582B2 (en) | 1999-04-06 | 2004-04-13 | Argose, Inc. | Non-invasive tissue glucose level monitoring |
US7899518B2 (en) | 1998-04-06 | 2011-03-01 | Masimo Laboratories, Inc. | Non-invasive tissue glucose level monitoring |
WO1999062399A1 (en) | 1998-06-03 | 1999-12-09 | Masimo Corporation | Stereo pulse oximeter |
US6128521A (en) | 1998-07-10 | 2000-10-03 | Physiometrix, Inc. | Self adjusting headgear appliance using reservoir electrodes |
US6285896B1 (en) | 1998-07-13 | 2001-09-04 | Masimo Corporation | Fetal pulse oximetry sensor |
US6129675A (en) | 1998-09-11 | 2000-10-10 | Jay; Gregory D. | Device and method for measuring pulsus paradoxus |
US6684091B2 (en) | 1998-10-15 | 2004-01-27 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage method |
US6343224B1 (en) | 1998-10-15 | 2002-01-29 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6519487B1 (en) | 1998-10-15 | 2003-02-11 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
USRE41912E1 (en) | 1998-10-15 | 2010-11-02 | Masimo Corporation | Reusable pulse oximeter probe and disposable bandage apparatus |
US6144868A (en) | 1998-10-15 | 2000-11-07 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6721585B1 (en) | 1998-10-15 | 2004-04-13 | Sensidyne, Inc. | Universal modular pulse oximeter probe for use with reusable and disposable patient attachment devices |
US6321100B1 (en) | 1999-07-13 | 2001-11-20 | Sensidyne, Inc. | Reusable pulse oximeter probe with disposable liner |
US7245953B1 (en) | 1999-04-12 | 2007-07-17 | Masimo Corporation | Reusable pulse oximeter probe and disposable bandage apparatii |
US6463311B1 (en) | 1998-12-30 | 2002-10-08 | Masimo Corporation | Plethysmograph pulse recognition processor |
US6684090B2 (en) | 1999-01-07 | 2004-01-27 | Masimo Corporation | Pulse oximetry data confidence indicator |
US6606511B1 (en) | 1999-01-07 | 2003-08-12 | Masimo Corporation | Pulse oximetry pulse indicator |
CA2684695C (en) | 1999-01-25 | 2012-11-06 | Masimo Corporation | Universal/upgrading pulse oximeter |
US6658276B2 (en) | 1999-01-25 | 2003-12-02 | Masimo Corporation | Pulse oximeter user interface |
US6770028B1 (en) | 1999-01-25 | 2004-08-03 | Masimo Corporation | Dual-mode pulse oximeter |
US20020140675A1 (en) | 1999-01-25 | 2002-10-03 | Ali Ammar Al | System and method for altering a display mode based on a gravity-responsive sensor |
US6360114B1 (en) | 1999-03-25 | 2002-03-19 | Masimo Corporation | Pulse oximeter probe-off detector |
JP2003502089A (en) | 1999-06-18 | 2003-01-21 | マシモ・コーポレイション | Pulse oximeter probe-off detection system |
US6301493B1 (en) | 1999-07-10 | 2001-10-09 | Physiometrix, Inc. | Reservoir electrodes for electroencephalograph headgear appliance |
US6515273B2 (en) | 1999-08-26 | 2003-02-04 | Masimo Corporation | System for indicating the expiration of the useful operating life of a pulse oximetry sensor |
US6374141B1 (en) * | 1999-10-08 | 2002-04-16 | Microhelix, Inc. | Multi-lead bioelectrical stimulus cable |
US6943348B1 (en) | 1999-10-19 | 2005-09-13 | Masimo Corporation | System for detecting injection holding material |
ATE326900T1 (en) | 1999-10-27 | 2006-06-15 | Hospira Sedation Inc | MODULE FOR OBTAINING ELECTROENCEPHALOGRAPHY SIGNALS FROM A PATIENT |
US6317627B1 (en) | 1999-11-02 | 2001-11-13 | Physiometrix, Inc. | Anesthesia monitoring system based on electroencephalographic signals |
US6639668B1 (en) | 1999-11-03 | 2003-10-28 | Argose, Inc. | Asynchronous fluorescence scan |
US6542764B1 (en) | 1999-12-01 | 2003-04-01 | Masimo Corporation | Pulse oximeter monitor for expressing the urgency of the patient's condition |
US6950687B2 (en) | 1999-12-09 | 2005-09-27 | Masimo Corporation | Isolation and communication element for a resposable pulse oximetry sensor |
US6377829B1 (en) | 1999-12-09 | 2002-04-23 | Masimo Corporation | Resposable pulse oximetry sensor |
US6671531B2 (en) | 1999-12-09 | 2003-12-30 | Masimo Corporation | Sensor wrap including foldable applicator |
US6152754A (en) | 1999-12-21 | 2000-11-28 | Masimo Corporation | Circuit board based cable connector |
EP1257192A1 (en) | 2000-02-18 | 2002-11-20 | Argose, Inc. | Generation of spatially-averaged excitation-emission map in heterogeneous tissue |
US20010034477A1 (en) | 2000-02-18 | 2001-10-25 | James Mansfield | Multivariate analysis of green to ultraviolet spectra of cell and tissue samples |
US6430525B1 (en) | 2000-06-05 | 2002-08-06 | Masimo Corporation | Variable mode averager |
US6470199B1 (en) | 2000-06-21 | 2002-10-22 | Masimo Corporation | Elastic sock for positioning an optical probe |
US6697656B1 (en) | 2000-06-27 | 2004-02-24 | Masimo Corporation | Pulse oximetry sensor compatible with multiple pulse oximetry systems |
DE60139128D1 (en) | 2000-08-18 | 2009-08-13 | Masimo Corp | PULSE OXIMETER WITH TWO OPERATING MODES |
US6640116B2 (en) | 2000-08-18 | 2003-10-28 | Masimo Corporation | Optical spectroscopy pathlength measurement system |
US6368283B1 (en) | 2000-09-08 | 2002-04-09 | Institut De Recherches Cliniques De Montreal | Method and apparatus for estimating systolic and mean pulmonary artery pressures of a patient |
US6760607B2 (en) | 2000-12-29 | 2004-07-06 | Masimo Corporation | Ribbon cable substrate pulse oximetry sensor |
EP1285446B1 (en) * | 2001-03-14 | 2005-11-02 | Leoni Kabel GmbH & Co KG | Transmission cable for medical signal values |
JP2004532526A (en) | 2001-05-03 | 2004-10-21 | マシモ・コーポレイション | Flex circuit shield optical sensor and method of manufacturing the flex circuit shield optical sensor |
US6850787B2 (en) | 2001-06-29 | 2005-02-01 | Masimo Laboratories, Inc. | Signal component processor |
US6697658B2 (en) | 2001-07-02 | 2004-02-24 | Masimo Corporation | Low power pulse oximeter |
US6595316B2 (en) | 2001-07-18 | 2003-07-22 | Andromed, Inc. | Tension-adjustable mechanism for stethoscope earpieces |
US20030212312A1 (en) * | 2002-01-07 | 2003-11-13 | Coffin James P. | Low noise patient cable |
US6934570B2 (en) | 2002-01-08 | 2005-08-23 | Masimo Corporation | Physiological sensor combination |
US6822564B2 (en) | 2002-01-24 | 2004-11-23 | Masimo Corporation | Parallel measurement alarm processor |
US7355512B1 (en) | 2002-01-24 | 2008-04-08 | Masimo Corporation | Parallel alarm processor |
US7015451B2 (en) | 2002-01-25 | 2006-03-21 | Masimo Corporation | Power supply rail controller |
US6961598B2 (en) | 2002-02-22 | 2005-11-01 | Masimo Corporation | Pulse and active pulse spectraphotometry |
US7509494B2 (en) | 2002-03-01 | 2009-03-24 | Masimo Corporation | Interface cable |
US8718738B2 (en) | 2002-03-08 | 2014-05-06 | Glt Acquisition Corp. | Method and apparatus for coupling a sample probe with a sample site |
US8504128B2 (en) | 2002-03-08 | 2013-08-06 | Glt Acquisition Corp. | Method and apparatus for coupling a channeled sample probe to tissue |
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
US6713673B2 (en) * | 2002-06-27 | 2004-03-30 | Capativa Tech, Inc. | Structure of speaker signal line |
US6661161B1 (en) | 2002-06-27 | 2003-12-09 | Andromed Inc. | Piezoelectric biological sound monitor with printed circuit board |
US7096054B2 (en) | 2002-08-01 | 2006-08-22 | Masimo Corporation | Low noise optical housing |
US7341559B2 (en) | 2002-09-14 | 2008-03-11 | Masimo Corporation | Pulse oximetry ear sensor |
US7274955B2 (en) | 2002-09-25 | 2007-09-25 | Masimo Corporation | Parameter compensated pulse oximeter |
US7142901B2 (en) | 2002-09-25 | 2006-11-28 | Masimo Corporation | Parameter compensated physiological monitor |
US7096052B2 (en) | 2002-10-04 | 2006-08-22 | Masimo Corporation | Optical probe including predetermined emission wavelength based on patient type |
WO2004044557A2 (en) | 2002-11-12 | 2004-05-27 | Argose, Inc. | Non-invasive measurement of analytes |
WO2004047631A2 (en) | 2002-11-22 | 2004-06-10 | Masimo Laboratories, Inc. | Blood parameter measurement system |
US6970792B1 (en) | 2002-12-04 | 2005-11-29 | Masimo Laboratories, Inc. | Systems and methods for determining blood oxygen saturation values using complex number encoding |
US7919713B2 (en) * | 2007-04-16 | 2011-04-05 | Masimo Corporation | Low noise oximetry cable including conductive cords |
US7225006B2 (en) | 2003-01-23 | 2007-05-29 | Masimo Corporation | Attachment and optical probe |
US6920345B2 (en) | 2003-01-24 | 2005-07-19 | Masimo Corporation | Optical sensor including disposable and reusable elements |
US20050061536A1 (en) * | 2003-09-19 | 2005-03-24 | Siemens Medical Solutions Usa, Inc. | Reduced crosstalk ultrasound cable |
US7003338B2 (en) | 2003-07-08 | 2006-02-21 | Masimo Corporation | Method and apparatus for reducing coupling between signals |
WO2005007215A2 (en) | 2003-07-09 | 2005-01-27 | Glucolight Corporation | Method and apparatus for tissue oximetry |
US7500950B2 (en) | 2003-07-25 | 2009-03-10 | Masimo Corporation | Multipurpose sensor port |
US7254431B2 (en) | 2003-08-28 | 2007-08-07 | Masimo Corporation | Physiological parameter tracking system |
US7254434B2 (en) | 2003-10-14 | 2007-08-07 | Masimo Corporation | Variable pressure reusable sensor |
US7483729B2 (en) | 2003-11-05 | 2009-01-27 | Masimo Corporation | Pulse oximeter access apparatus and method |
US7373193B2 (en) | 2003-11-07 | 2008-05-13 | Masimo Corporation | Pulse oximetry data capture system |
US8029765B2 (en) | 2003-12-24 | 2011-10-04 | Masimo Laboratories, Inc. | SMMR (small molecule metabolite reporters) for use as in vivo glucose biosensors |
US7280858B2 (en) | 2004-01-05 | 2007-10-09 | Masimo Corporation | Pulse oximetry sensor |
US7510849B2 (en) | 2004-01-29 | 2009-03-31 | Glucolight Corporation | OCT based method for diagnosis and therapy |
US7371981B2 (en) | 2004-02-20 | 2008-05-13 | Masimo Corporation | Connector switch |
US7438683B2 (en) | 2004-03-04 | 2008-10-21 | Masimo Corporation | Application identification sensor |
EP1722676B1 (en) | 2004-03-08 | 2012-12-19 | Masimo Corporation | Physiological parameter system |
US7292883B2 (en) | 2004-03-31 | 2007-11-06 | Masimo Corporation | Physiological assessment system |
CA2464029A1 (en) | 2004-04-08 | 2005-10-08 | Valery Telfort | Non-invasive ventilation monitor |
CA2464634A1 (en) | 2004-04-16 | 2005-10-16 | Andromed Inc. | Pap estimator |
US8868147B2 (en) | 2004-04-28 | 2014-10-21 | Glt Acquisition Corp. | Method and apparatus for controlling positioning of a noninvasive analyzer sample probe |
US7343186B2 (en) | 2004-07-07 | 2008-03-11 | Masimo Laboratories, Inc. | Multi-wavelength physiological monitor |
US9341565B2 (en) | 2004-07-07 | 2016-05-17 | Masimo Corporation | Multiple-wavelength physiological monitor |
US7937128B2 (en) | 2004-07-09 | 2011-05-03 | Masimo Corporation | Cyanotic infant sensor |
US7254429B2 (en) | 2004-08-11 | 2007-08-07 | Glucolight Corporation | Method and apparatus for monitoring glucose levels in a biological tissue |
US8036727B2 (en) | 2004-08-11 | 2011-10-11 | Glt Acquisition Corp. | Methods for noninvasively measuring analyte levels in a subject |
US7976472B2 (en) | 2004-09-07 | 2011-07-12 | Masimo Corporation | Noninvasive hypovolemia monitor |
US7351912B2 (en) * | 2005-02-10 | 2008-04-01 | Zoll Medical Corporation | Medical cable |
USD554263S1 (en) | 2005-02-18 | 2007-10-30 | Masimo Corporation | Portable patient monitor |
US20060189871A1 (en) | 2005-02-18 | 2006-08-24 | Ammar Al-Ali | Portable patient monitor |
USD566282S1 (en) | 2005-02-18 | 2008-04-08 | Masimo Corporation | Stand for a portable patient monitor |
US7761127B2 (en) | 2005-03-01 | 2010-07-20 | Masimo Laboratories, Inc. | Multiple wavelength sensor substrate |
US7937129B2 (en) | 2005-03-21 | 2011-05-03 | Masimo Corporation | Variable aperture sensor |
CA2604653A1 (en) | 2005-04-13 | 2006-10-19 | Glucolight Corporation | Method for data reduction and calibration of an oct-based blood glucose monitor |
US7962188B2 (en) | 2005-10-14 | 2011-06-14 | Masimo Corporation | Robust alarm system |
US7530942B1 (en) | 2005-10-18 | 2009-05-12 | Masimo Corporation | Remote sensing infant warmer |
WO2007064984A2 (en) | 2005-11-29 | 2007-06-07 | Masimo Corporation | Optical sensor including disposable and reusable elements |
US7990382B2 (en) | 2006-01-03 | 2011-08-02 | Masimo Corporation | Virtual display |
US8182443B1 (en) | 2006-01-17 | 2012-05-22 | Masimo Corporation | Drug administration controller |
US8219172B2 (en) | 2006-03-17 | 2012-07-10 | Glt Acquisition Corp. | System and method for creating a stable optical interface |
US7941199B2 (en) | 2006-05-15 | 2011-05-10 | Masimo Laboratories, Inc. | Sepsis monitor |
US8998809B2 (en) | 2006-05-15 | 2015-04-07 | Cercacor Laboratories, Inc. | Systems and methods for calibrating minimally invasive and non-invasive physiological sensor devices |
US9176141B2 (en) | 2006-05-15 | 2015-11-03 | Cercacor Laboratories, Inc. | Physiological monitor calibration system |
US8028701B2 (en) | 2006-05-31 | 2011-10-04 | Masimo Corporation | Respiratory monitoring |
USD587657S1 (en) | 2007-10-12 | 2009-03-03 | Masimo Corporation | Connector assembly |
USD614305S1 (en) | 2008-02-29 | 2010-04-20 | Masimo Corporation | Connector assembly |
US8457707B2 (en) | 2006-09-20 | 2013-06-04 | Masimo Corporation | Congenital heart disease monitor |
US8315683B2 (en) | 2006-09-20 | 2012-11-20 | Masimo Corporation | Duo connector patient cable |
USD609193S1 (en) | 2007-10-12 | 2010-02-02 | Masimo Corporation | Connector assembly |
US9161696B2 (en) | 2006-09-22 | 2015-10-20 | Masimo Corporation | Modular patient monitor |
US8840549B2 (en) | 2006-09-22 | 2014-09-23 | Masimo Corporation | Modular patient monitor |
US8265723B1 (en) | 2006-10-12 | 2012-09-11 | Cercacor Laboratories, Inc. | Oximeter probe off indicator defining probe off space |
US8280473B2 (en) | 2006-10-12 | 2012-10-02 | Masino Corporation, Inc. | Perfusion index smoother |
US8255026B1 (en) | 2006-10-12 | 2012-08-28 | Masimo Corporation, Inc. | Patient monitor capable of monitoring the quality of attached probes and accessories |
US7880626B2 (en) | 2006-10-12 | 2011-02-01 | Masimo Corporation | System and method for monitoring the life of a physiological sensor |
US8600467B2 (en) | 2006-11-29 | 2013-12-03 | Cercacor Laboratories, Inc. | Optical sensor including disposable and reusable elements |
EP2096994B1 (en) | 2006-12-09 | 2018-10-03 | Masimo Corporation | Plethysmograph variability determination |
US7791155B2 (en) | 2006-12-22 | 2010-09-07 | Masimo Laboratories, Inc. | Detector shield |
US8852094B2 (en) | 2006-12-22 | 2014-10-07 | Masimo Corporation | Physiological parameter system |
US8652060B2 (en) | 2007-01-20 | 2014-02-18 | Masimo Corporation | Perfusion trend indicator |
EP2139383B1 (en) | 2007-03-27 | 2013-02-13 | Masimo Laboratories, Inc. | Multiple wavelength optical sensor |
US8374665B2 (en) | 2007-04-21 | 2013-02-12 | Cercacor Laboratories, Inc. | Tissue profile wellness monitor |
US8764671B2 (en) | 2007-06-28 | 2014-07-01 | Masimo Corporation | Disposable active pulse sensor |
US8048040B2 (en) | 2007-09-13 | 2011-11-01 | Masimo Corporation | Fluid titration system |
US8310336B2 (en) | 2008-10-10 | 2012-11-13 | Masimo Corporation | Systems and methods for storing, analyzing, retrieving and displaying streaming medical data |
JP5296793B2 (en) | 2007-10-12 | 2013-09-25 | マシモ コーポレイション | Connector assembly |
US8274360B2 (en) | 2007-10-12 | 2012-09-25 | Masimo Corporation | Systems and methods for storing, analyzing, and retrieving medical data |
US8355766B2 (en) | 2007-10-12 | 2013-01-15 | Masimo Corporation | Ceramic emitter substrate |
US20090247984A1 (en) | 2007-10-24 | 2009-10-01 | Masimo Laboratories, Inc. | Use of microneedles for small molecule metabolite reporter delivery |
US8768423B2 (en) | 2008-03-04 | 2014-07-01 | Glt Acquisition Corp. | Multispot monitoring for use in optical coherence tomography |
WO2009134724A1 (en) | 2008-05-02 | 2009-11-05 | Masimo Corporation | Monitor configuration system |
US9107625B2 (en) | 2008-05-05 | 2015-08-18 | Masimo Corporation | Pulse oximetry system with electrical decoupling circuitry |
USD606659S1 (en) | 2008-08-25 | 2009-12-22 | Masimo Laboratories, Inc. | Patient monitor |
USD621516S1 (en) | 2008-08-25 | 2010-08-10 | Masimo Laboratories, Inc. | Patient monitoring sensor |
US20100004518A1 (en) | 2008-07-03 | 2010-01-07 | Masimo Laboratories, Inc. | Heat sink for noninvasive medical sensor |
US8203438B2 (en) | 2008-07-29 | 2012-06-19 | Masimo Corporation | Alarm suspend system |
US8630691B2 (en) | 2008-08-04 | 2014-01-14 | Cercacor Laboratories, Inc. | Multi-stream sensor front ends for noninvasive measurement of blood constituents |
US8911377B2 (en) | 2008-09-15 | 2014-12-16 | Masimo Corporation | Patient monitor including multi-parameter graphical display |
US8401602B2 (en) | 2008-10-13 | 2013-03-19 | Masimo Corporation | Secondary-emitter sensor position indicator |
US8346330B2 (en) | 2008-10-13 | 2013-01-01 | Masimo Corporation | Reflection-detector sensor position indicator |
US8771204B2 (en) | 2008-12-30 | 2014-07-08 | Masimo Corporation | Acoustic sensor assembly |
US8588880B2 (en) | 2009-02-16 | 2013-11-19 | Masimo Corporation | Ear sensor |
US10007758B2 (en) | 2009-03-04 | 2018-06-26 | Masimo Corporation | Medical monitoring system |
US9218454B2 (en) | 2009-03-04 | 2015-12-22 | Masimo Corporation | Medical monitoring system |
US10032002B2 (en) | 2009-03-04 | 2018-07-24 | Masimo Corporation | Medical monitoring system |
US9323894B2 (en) | 2011-08-19 | 2016-04-26 | Masimo Corporation | Health care sanitation monitoring system |
US8388353B2 (en) | 2009-03-11 | 2013-03-05 | Cercacor Laboratories, Inc. | Magnetic connector |
US8897847B2 (en) | 2009-03-23 | 2014-11-25 | Masimo Corporation | Digit gauge for noninvasive optical sensor |
WO2010135373A1 (en) | 2009-05-19 | 2010-11-25 | Masimo Corporation | Disposable components for reusable physiological sensor |
US8571619B2 (en) | 2009-05-20 | 2013-10-29 | Masimo Corporation | Hemoglobin display and patient treatment |
US8418524B2 (en) | 2009-06-12 | 2013-04-16 | Masimo Corporation | Non-invasive sensor calibration device |
US8670811B2 (en) | 2009-06-30 | 2014-03-11 | Masimo Corporation | Pulse oximetry system for adjusting medical ventilation |
US20110208015A1 (en) | 2009-07-20 | 2011-08-25 | Masimo Corporation | Wireless patient monitoring system |
US8471713B2 (en) | 2009-07-24 | 2013-06-25 | Cercacor Laboratories, Inc. | Interference detector for patient monitor |
US8473020B2 (en) | 2009-07-29 | 2013-06-25 | Cercacor Laboratories, Inc. | Non-invasive physiological sensor cover |
US20110028806A1 (en) | 2009-07-29 | 2011-02-03 | Sean Merritt | Reflectance calibration of fluorescence-based glucose measurements |
US8688183B2 (en) | 2009-09-03 | 2014-04-01 | Ceracor Laboratories, Inc. | Emitter driver for noninvasive patient monitor |
US20110172498A1 (en) | 2009-09-14 | 2011-07-14 | Olsen Gregory A | Spot check monitor credit system |
US9579039B2 (en) | 2011-01-10 | 2017-02-28 | Masimo Corporation | Non-invasive intravascular volume index monitor |
US8571618B1 (en) | 2009-09-28 | 2013-10-29 | Cercacor Laboratories, Inc. | Adaptive calibration system for spectrophotometric measurements |
US20110082711A1 (en) | 2009-10-06 | 2011-04-07 | Masimo Laboratories, Inc. | Personal digital assistant or organizer for monitoring glucose levels |
US10463340B2 (en) | 2009-10-15 | 2019-11-05 | Masimo Corporation | Acoustic respiratory monitoring systems and methods |
WO2011047211A1 (en) | 2009-10-15 | 2011-04-21 | Masimo Corporation | Pulse oximetry system with low noise cable hub |
US9066680B1 (en) | 2009-10-15 | 2015-06-30 | Masimo Corporation | System for determining confidence in respiratory rate measurements |
EP2488106B1 (en) | 2009-10-15 | 2020-07-08 | Masimo Corporation | Acoustic respiratory monitoring sensor having multiple sensing elements |
US8790268B2 (en) | 2009-10-15 | 2014-07-29 | Masimo Corporation | Bidirectional physiological information display |
DE112010004682T5 (en) | 2009-12-04 | 2013-03-28 | Masimo Corporation | Calibration for multi-level physiological monitors |
DE112011100282T5 (en) | 2010-01-19 | 2012-11-29 | Masimo Corporation | Wellness assessment system |
DE112011100761T5 (en) | 2010-03-01 | 2013-01-03 | Masimo Corporation | Adaptive alarm system |
WO2011112524A1 (en) | 2010-03-08 | 2011-09-15 | Masimo Corporation | Reprocessing of a physiological sensor |
US8712494B1 (en) | 2010-05-03 | 2014-04-29 | Masimo Corporation | Reflective non-invasive sensor |
US8666468B1 (en) | 2010-05-06 | 2014-03-04 | Masimo Corporation | Patient monitor for determining microcirculation state |
US8852994B2 (en) | 2010-05-24 | 2014-10-07 | Masimo Semiconductor, Inc. | Method of fabricating bifacial tandem solar cells |
US8740792B1 (en) | 2010-07-12 | 2014-06-03 | Masimo Corporation | Patient monitor capable of accounting for environmental conditions |
WO2012027613A1 (en) | 2010-08-26 | 2012-03-01 | Masimo Corporation | Blood pressure measurement system |
US8455290B2 (en) | 2010-09-04 | 2013-06-04 | Masimo Semiconductor, Inc. | Method of fabricating epitaxial structures |
JP5710767B2 (en) | 2010-09-28 | 2015-04-30 | マシモ コーポレイション | Depth of consciousness monitor including oximeter |
US8723677B1 (en) | 2010-10-20 | 2014-05-13 | Masimo Corporation | Patient safety system with automatically adjusting bed |
US20120209084A1 (en) | 2011-01-21 | 2012-08-16 | Masimo Corporation | Respiratory event alert system |
WO2012109671A1 (en) | 2011-02-13 | 2012-08-16 | Masimo Corporation | Medical characterization system |
US9066666B2 (en) | 2011-02-25 | 2015-06-30 | Cercacor Laboratories, Inc. | Patient monitor for monitoring microcirculation |
US8830449B1 (en) | 2011-04-18 | 2014-09-09 | Cercacor Laboratories, Inc. | Blood analysis system |
EP2699161A1 (en) | 2011-04-18 | 2014-02-26 | Cercacor Laboratories, Inc. | Pediatric monitor sensor steady game |
US9095316B2 (en) | 2011-04-20 | 2015-08-04 | Masimo Corporation | System for generating alarms based on alarm patterns |
US9622692B2 (en) | 2011-05-16 | 2017-04-18 | Masimo Corporation | Personal health device |
US9532722B2 (en) | 2011-06-21 | 2017-01-03 | Masimo Corporation | Patient monitoring system |
US9986919B2 (en) | 2011-06-21 | 2018-06-05 | Masimo Corporation | Patient monitoring system |
US11439329B2 (en) | 2011-07-13 | 2022-09-13 | Masimo Corporation | Multiple measurement mode in a physiological sensor |
US20130023775A1 (en) | 2011-07-20 | 2013-01-24 | Cercacor Laboratories, Inc. | Magnetic Reusable Sensor |
US8755872B1 (en) | 2011-07-28 | 2014-06-17 | Masimo Corporation | Patient monitoring system for indicating an abnormal condition |
WO2013019991A1 (en) | 2011-08-04 | 2013-02-07 | Masimo Corporation | Occlusive non-inflatable blood pressure device |
US20130096405A1 (en) | 2011-08-12 | 2013-04-18 | Masimo Corporation | Fingertip pulse oximeter |
US9782077B2 (en) | 2011-08-17 | 2017-10-10 | Masimo Corporation | Modulated physiological sensor |
EP3603502B1 (en) | 2011-10-13 | 2023-10-04 | Masimo Corporation | Physiological acoustic monitoring system |
US9392945B2 (en) | 2012-01-04 | 2016-07-19 | Masimo Corporation | Automated CCHD screening and detection |
US10149616B2 (en) | 2012-02-09 | 2018-12-11 | Masimo Corporation | Wireless patient monitoring device |
US9480435B2 (en) | 2012-02-09 | 2016-11-01 | Masimo Corporation | Configurable patient monitoring system |
JP6490577B2 (en) | 2012-04-17 | 2019-03-27 | マシモ・コーポレイション | How to operate a pulse oximeter device |
US20130296672A1 (en) | 2012-05-02 | 2013-11-07 | Masimo Corporation | Noninvasive physiological sensor cover |
US9697928B2 (en) | 2012-08-01 | 2017-07-04 | Masimo Corporation | Automated assembly sensor cable |
US9749232B2 (en) | 2012-09-20 | 2017-08-29 | Masimo Corporation | Intelligent medical network edge router |
USD692145S1 (en) | 2012-09-20 | 2013-10-22 | Masimo Corporation | Medical proximity detection token |
US9877650B2 (en) | 2012-09-20 | 2018-01-30 | Masimo Corporation | Physiological monitor with mobile computing device connectivity |
US9955937B2 (en) | 2012-09-20 | 2018-05-01 | Masimo Corporation | Acoustic patient sensor coupler |
US9717458B2 (en) | 2012-10-20 | 2017-08-01 | Masimo Corporation | Magnetic-flap optical sensor |
US9560996B2 (en) | 2012-10-30 | 2017-02-07 | Masimo Corporation | Universal medical system |
US9787568B2 (en) | 2012-11-05 | 2017-10-10 | Cercacor Laboratories, Inc. | Physiological test credit method |
US20140166076A1 (en) | 2012-12-17 | 2014-06-19 | Masimo Semiconductor, Inc | Pool solar power generator |
WO2014164139A1 (en) | 2013-03-13 | 2014-10-09 | Masimo Corporation | Systems and methods for monitoring a patient health network |
US20140275871A1 (en) | 2013-03-14 | 2014-09-18 | Cercacor Laboratories, Inc. | Wireless optical communication between noninvasive physiological sensors and patient monitors |
US9936917B2 (en) | 2013-03-14 | 2018-04-10 | Masimo Laboratories, Inc. | Patient monitor placement indicator |
WO2014159132A1 (en) | 2013-03-14 | 2014-10-02 | Cercacor Laboratories, Inc. | Systems and methods for testing patient monitors |
WO2014158820A1 (en) | 2013-03-14 | 2014-10-02 | Cercacor Laboratories, Inc. | Patient monitor as a minimally invasive glucometer |
US10456038B2 (en) | 2013-03-15 | 2019-10-29 | Cercacor Laboratories, Inc. | Cloud-based physiological monitoring system |
-
2012
- 2012-06-28 US US13/536,881 patent/US9245668B1/en active Active
-
2016
- 2016-01-21 US US15/003,747 patent/US20160284441A1/en not_active Abandoned
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20170014623A1 (en) * | 2012-04-19 | 2017-01-19 | Medtronic, Inc. | Paired medical lead bodies with braided conductive shields having different physical parameter values |
US9907956B2 (en) * | 2012-04-19 | 2018-03-06 | Medtronic, Inc. | Paired medical lead bodies with braided conductive shields having different physical parameter values |
WO2023042040A1 (en) * | 2021-09-17 | 2023-03-23 | Know Labs, Inc. | Noise reduction in non-invasive radio frequency analyte sensors |
Also Published As
Publication number | Publication date |
---|---|
US9245668B1 (en) | 2016-01-26 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US9245668B1 (en) | Low noise cable providing communication between electronic sensor components and patient monitor | |
US11389093B2 (en) | Low noise oximetry cable | |
US7919713B2 (en) | Low noise oximetry cable including conductive cords | |
US20230230726A1 (en) | Automated assembly sensor cable | |
WO2022240765A1 (en) | Optical physiological nose sensor | |
US8781548B2 (en) | Medical sensor with flexible components and technique for using the same | |
CN216317552U (en) | Medical device system for detecting damage and potential damage to optical fiber technology of medical devices | |
US8219170B2 (en) | System and method for practicing spectrophotometry using light emitting nanostructure devices | |
CN112386335A (en) | Shape sensing systems and methods for medical devices | |
WO2012047851A1 (en) | Continuous measurement of total hemoglobin | |
US8588879B2 (en) | Motion compensation in a sensor | |
US10864056B2 (en) | Low-complexity optical force sensor for a medical device | |
US8805465B2 (en) | Multiple sensor assemblies and cables in a single sensor body | |
KR20190098512A (en) | Mapping catheter | |
JP7292856B2 (en) | Reducing noise levels associated with sensed ECG signals | |
US7880884B2 (en) | System and method for coating and shielding electronic sensor components | |
CN210043995U (en) | Cable unit and wearable physiological parameter monitoring system | |
WO2021193201A1 (en) | Vital sensor | |
CN104706361A (en) | Optical sensor | |
CN219206913U (en) | Wearable physiological parameter monitoring equipment and lead cable | |
CN110970161B (en) | Blood oxygen cable, wearable blood oxygen detector and cable cabling method | |
KR20200061019A (en) | Apparatus for measuring bio-signal | |
CN209525950U (en) | Cable unit and wearable physiological parameter monitoring system | |
US11009561B2 (en) | Cable identification tester | |
CN220778342U (en) | Electrocardiogram lead wire for nuclear magnetic resonance |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: MASIMO CORPORATION, CALIFORNIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:CERCACOR LABORATORIES, INC.;REEL/FRAME:038049/0074 Effective date: 20160308 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |