US20230337966A1 - SEM Scanner Sensing Apparatus, System and Methodology for Early Detection of Ulcers - Google Patents
SEM Scanner Sensing Apparatus, System and Methodology for Early Detection of Ulcers Download PDFInfo
- Publication number
- US20230337966A1 US20230337966A1 US18/346,103 US202318346103A US2023337966A1 US 20230337966 A1 US20230337966 A1 US 20230337966A1 US 202318346103 A US202318346103 A US 202318346103A US 2023337966 A1 US2023337966 A1 US 2023337966A1
- Authority
- US
- United States
- Prior art keywords
- sensor
- skin
- subject
- array
- sensors
- 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.)
- Pending
Links
- 238000000034 method Methods 0.000 title claims description 24
- 208000025865 Ulcer Diseases 0.000 title claims description 12
- 231100000397 ulcer Toxicity 0.000 title claims description 12
- 238000001514 detection method Methods 0.000 title description 3
- 208000004210 Pressure Ulcer Diseases 0.000 claims abstract description 12
- 238000011161 development Methods 0.000 claims description 7
- 238000012546 transfer Methods 0.000 claims description 4
- 238000004891 communication Methods 0.000 claims description 2
- 206010011985 Decubitus ulcer Diseases 0.000 claims 1
- 230000015572 biosynthetic process Effects 0.000 abstract description 4
- 239000000758 substrate Substances 0.000 description 74
- 239000010410 layer Substances 0.000 description 32
- 229920003223 poly(pyromellitimide-1,4-diphenyl ether) Polymers 0.000 description 20
- 238000005259 measurement Methods 0.000 description 18
- 206010052428 Wound Diseases 0.000 description 11
- 208000027418 Wounds and injury Diseases 0.000 description 11
- 229920001296 polysiloxane Polymers 0.000 description 11
- 239000003351 stiffener Substances 0.000 description 11
- 239000006210 lotion Substances 0.000 description 10
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 9
- 229910052802 copper Inorganic materials 0.000 description 9
- 239000010949 copper Substances 0.000 description 9
- 125000006850 spacer group Chemical group 0.000 description 9
- 230000008859 change Effects 0.000 description 6
- 230000004044 response Effects 0.000 description 6
- 238000012544 monitoring process Methods 0.000 description 5
- 206010013786 Dry skin Diseases 0.000 description 4
- 239000004642 Polyimide Substances 0.000 description 4
- 230000037336 dry skin Effects 0.000 description 4
- 229920001721 polyimide Polymers 0.000 description 4
- 230000036962 time dependent Effects 0.000 description 4
- 239000004909 Moisturizer Substances 0.000 description 3
- 239000012790 adhesive layer Substances 0.000 description 3
- 210000003484 anatomy Anatomy 0.000 description 3
- 238000002474 experimental method Methods 0.000 description 3
- 210000000245 forearm Anatomy 0.000 description 3
- 238000003384 imaging method Methods 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 230000001333 moisturizer Effects 0.000 description 3
- 230000000474 nursing effect Effects 0.000 description 3
- 230000035945 sensitivity Effects 0.000 description 3
- 208000024891 symptom Diseases 0.000 description 3
- 238000012360 testing method Methods 0.000 description 3
- 230000004075 alteration Effects 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 2
- 230000008901 benefit Effects 0.000 description 2
- 230000003449 preventive effect Effects 0.000 description 2
- 238000007789 sealing Methods 0.000 description 2
- 208000008960 Diabetic foot Diseases 0.000 description 1
- 206010040943 Skin Ulcer Diseases 0.000 description 1
- 230000001154 acute effect Effects 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 230000001684 chronic effect Effects 0.000 description 1
- 238000004140 cleaning Methods 0.000 description 1
- 238000004590 computer program Methods 0.000 description 1
- 238000005520 cutting process Methods 0.000 description 1
- 229910003460 diamond Inorganic materials 0.000 description 1
- 239000010432 diamond Substances 0.000 description 1
- 239000003989 dielectric material Substances 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 230000005284 excitation Effects 0.000 description 1
- 210000003811 finger Anatomy 0.000 description 1
- 230000005802 health problem Effects 0.000 description 1
- 238000011065 in-situ storage Methods 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 230000002757 inflammatory effect Effects 0.000 description 1
- 238000012423 maintenance Methods 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 238000013507 mapping Methods 0.000 description 1
- 230000007246 mechanism Effects 0.000 description 1
- 238000003909 pattern recognition Methods 0.000 description 1
- 230000002980 postoperative effect Effects 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
- 229920006395 saturated elastomer Polymers 0.000 description 1
- 208000017520 skin disease Diseases 0.000 description 1
- 231100000019 skin ulcer Toxicity 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 210000003813 thumb Anatomy 0.000 description 1
- 238000011282 treatment Methods 0.000 description 1
- 238000002604 ultrasonography Methods 0.000 description 1
- 230000029663 wound healing Effects 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
- A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
- A61B5/447—Skin evaluation, e.g. for skin disorder diagnosis specially adapted for aiding the prevention of ulcer or pressure sore development, i.e. before the ulcer or sore has developed
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/053—Measuring electrical impedance or conductance of a portion of the body
- A61B5/0531—Measuring skin impedance
- A61B5/0533—Measuring galvanic skin response
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/053—Measuring electrical impedance or conductance of a portion of the body
- A61B5/0537—Measuring body composition by impedance, e.g. tissue hydration or fat content
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
- A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
- A61B5/443—Evaluating skin constituents, e.g. elastin, melanin, water
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
- A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
- A61B5/445—Evaluating skin irritation or skin trauma, e.g. rash, eczema, wound, bed sore
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6843—Monitoring or controlling sensor contact pressure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6844—Monitoring or controlling distance between sensor and tissue
-
- 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
- A61B5/7271—Specific aspects of physiological measurement analysis
-
- 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
- A61B5/7271—Specific aspects of physiological measurement analysis
- A61B5/7285—Specific aspects of physiological measurement analysis for synchronising or triggering a physiological measurement or image acquisition with a physiological event or waveform, e.g. an ECG signal
-
- 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
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
- A61B2562/0209—Special features of electrodes classified in A61B5/24, A61B5/25, A61B5/283, A61B5/291, A61B5/296, A61B5/053
- A61B2562/0214—Capacitive electrodes
-
- 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
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
- A61B2562/0247—Pressure sensors
-
- 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
- A61B2562/04—Arrangements of multiple sensors of the same type
-
- 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
- A61B2562/04—Arrangements of multiple sensors of the same type
- A61B2562/046—Arrangements of multiple sensors of the same type in a matrix array
-
- 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
- A61B2562/06—Arrangements of multiple sensors of different types
- A61B2562/066—Arrangements of multiple sensors of different types in a matrix array
-
- 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
- A61B2562/16—Details of sensor housings or probes; Details of structural supports for sensors
- A61B2562/164—Details of sensor housings or probes; Details of structural supports for sensors the sensor is mounted in or on a conformable substrate or carrier
Definitions
- This invention pertains generally to monitoring skin pressure ulcers and more particularly to skin ulcer monitoring via measurement of Sub-epidermal Moisture (SEM).
- SEM Sub-epidermal Moisture
- An aspect of the present invention is a smart compact capacitive sensing conforming handheld apparatus configured to measure Sub-epidermal Moisture (SEM) as a mean to detect and monitor the development of pressure ulcers.
- the device incorporates an array of electrodes which are excited to measure and scan SEM in a programmable and multiplexed manner by a battery-less RF-powered chip.
- the scanning operation is initiated by an interrogator which excites a coil embedded in the apparatus and provides the needed energy burst to support the scanning/reading operation.
- Each embedded electrode measures the equivalent sub-epidermal capacitance corresponding and representing the moisture content of the target surface.
- An aspect of this invention is the in situ sensing and monitoring of skin or wound or ulcer development status using a wireless, biocompatible RF powered capacitive sensing system referred to as smart SEM imager.
- the present invention enables the realization of smart preventive measures by enabling early detection of ulcer formation or inflammatory pressure which would otherwise have not been detected for an extended period with increased risk of infection and higher stage ulcer development.
- the handheld capacitive sensing imager apparatus incorporates pressure sensing components in conjunction with the sensing electrodes to monitor the level of applied pressure on each electrode in order to guarantee precise wound or skin electrical capacitance measurements to characterize moisture content.
- pressure sensing components in conjunction with the sensing electrodes to monitor the level of applied pressure on each electrode in order to guarantee precise wound or skin electrical capacitance measurements to characterize moisture content.
- such embodiment would enable new capabilities including but not limited to: 1) measurement capabilities such as SEM imaging and SEM depth imaging determined by electrode geometry and dielectrics, and 2) signal processing and pattern recognition having automatic and assured registration exploiting pressure imaging and automatic assurance of usage exploiting software systems providing usage tracking.
- the apparatus includes a bipolar RF sensor embedded on a flexible substrate, and a conformal pressure pad disposed adjacent and underneath the substrate, wherein the conformal pressure pad is configured to support the flexible substrate while allowing the flexible substrate to conform to a non-planar sensing surface of the patient’s skin.
- the apparatus further includes interface electronics coupled to the sensor; wherein the interface electronics are configured to control emission and reception of RF energy to interrogate the patient’s skin.
- Another aspect is a method for monitoring the formation of pressure ulcers at a target location of a patient’s skin.
- the method includes the steps of positioning a flexible substrate adjacent the target location of the patient’s skin; the flexible substrate comprising one or more bipolar RF sensors; conforming the flexible substrate to the patient’s skin at the target location; exciting the one or more bipolar RF sensor to emit RF energy into the patient’s skin; and measuring the capacitance of the skin at the target location as an indicator of the Sub-Epidermal Moisture (SEM) at the target location.
- SEM Sub-Epidermal Moisture
- FIG. 1 illustrates an assembled perspective component view of the SEM Scanner of the present invention.
- FIG. 2 illustrates a perspective view of a Kapton-based conforming sensing substrate assembly of the present invention.
- FIG. 3 shows a top view of an exemplary concentric sensing electrode in accordance with the present invention.
- FIG. 4 illustrates a side view of a flex stack-up for the Kapton-based conforming sensing substrate shown in FIG. 2 .
- FIG. 5 illustrates a side view of an alternative flex stack-up for a Kapton-based conforming sensing substrate.
- FIG. 6 shows a top view of two-electrode sensing Kapton-based flex sensor substrates for three alternative types of capacitive sensing concentric electrodes.
- FIG. 7 illustrates an exploded perspective component view of the SEM scanner of FIG. 1 .
- FIG. 8 illustrates a schematic side view of the SEM scanner of FIG. 1 .
- FIG. 9 illustrates a schematic side view of the SEM scanner of FIG. 8 in contact with subject skin.
- FIG. 10 illustrates a perspective view of an assembled SEM scanner with an alternative array of sensors in accordance with the present invention.
- FIG. 11 is a plot of normalized responses of the tested electrodes of the present invention.
- FIG. 12 is a graph of measured equivalent capacitance for dry volar arm for three different concentric sensor electrodes.
- FIG. 13 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 30 minutes of applying lotion).
- FIG. 14 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 15 minutes of applying lotion).
- FIG. 15 is a plot of fractional change vs. time.
- FIG. 16 shows a SEM scanner electrode system and electrode layering providing proper shielding from interference.
- FIG. 17 shows an SEM scanner mechanical compliance for electrodes developed to enable probing of bony prominence.
- FIG. 18 is an overview of the wound registration method according to an embodiment of the description.
- FIG. 19 illustrates pressure and moisture measurements obtained according to an embodiment of the description.
- FIG. 20 illustrates sample measurements over two different days.
- a smart handheld capacitive sensing device employs a programmable sensing electrode array. This is based on methods that use an interrogator to excite the embedded electrodes.
- FIG. 1 and FIG. 7 illustrate an SEM scanning/sensing apparatus 10 according to the present invention.
- the apparatus 10 comprises five main components, including a top silicone edge sealing gasket 18 encircling a Kapton-based sensing substrate 16 , which rests on a conformal silicone pressure pad 12 .
- a thick annular silicone spacer 20 is disposed under the pressure pad to provide free space for the pressure pad to deform.
- the bottom layer comprises an interface electronics package enclosure 22 that houses interface circuitry for interrogating and transmitting data for evaluation.
- an array 14 of individual RF electrode sensors 24 and 26 is embedded on a flexible biocompatible substrate 16 .
- Substrate 16 may comprise a laminated Kapton (Polyimide) chip-on-flex.
- FIG. 2 illustrates one embodiment of a Kapton sensor substrate 16a that comprises an array 14 of differing sized concentric sensing electrodes.
- a flexible biocompatible Polyimide or Kapton substrate 32 comprises a layer of sensing electrodes coated on one side with an ultra thin cover layer 30 of Polyimide (e.g. CA335) to isolate the electrodes from direct moisture contact and also to provide a uniform contact surface.
- Polyimide e.g. CA335
- sample capacitive sensing electrodes of different sizes are shown in an array 14 , and which are manipulated to achieve and sense different depths of skin.
- the array of sensing electrodes 14 may comprise any number of different shape and configurations, such as the concentric circles 24 , 26 , 29 , or the interdigitating fingers of sensor 15 .
- FIG. 3 illustrates a close-up top view of a concentric sensing pad 26 in accordance with the present invention.
- Pad 26 comprises a bipolar configuration having a first electrode 36 comprising an outer annular ring disposed around a second inner circular electrode 38 .
- Outer ring electrode 36 has an outer diameter D o and an inner diameter D i that is larger than the diameter D c of the circular inner electrode 38 to form annular gap 40 .
- Inner circular electrode 38 and outer ring electrode 36 are coupled electrically to interface electronics in the interface electronics package 22 . As shown in greater detail in FIGS. 4 and 5 , electrodes 36 and 38 are disposed on separate layers within the substrate assembly 16 .
- the dimensions of the sensor pads 24 , 26 generally correspond to the depth of interrogation into the derma of the patient. Accordingly, a larger diameter pad (e.g. pad 26 or 29 ) will penetrate deeper into the skin than a smaller pad. The desired depth may vary depending on the region of the body being scanned, or the age, skin anatomy or other characteristic of the patient.
- SEM scanner 10 may comprise an array of different sized pads (e.g. small pads 24 and medium sized pads 26 shown in FIG. 1 ) each individually coupled to the interface electronics package 22 .
- FIG. 4 illustrates side view of a flex stack-up for a Kapton based substrate assembly 16 , where thin adhesive layers 42 are used to attach a Kapton layer 32 in between copper layers 44 and 46 , all of which are disposed between upper coverlay 30 and lower coverlay 48 .
- a stiffener 50 is disposed under lower coverlay 48 , being positioned directly under copper layer 46 of the sensing pads.
- the stiffener 50 forms a rigid portion of the substrate where sensing pad array 14 , connectors (e.g. connectors 66 , 76 , or 86 shown in FIG. 6 ) and interfacing (e.g. lead wires 34 ) are located, so that these areas do not deform, whereas the rest of the substrate is free to deform.
- the top copper layer 44 is used to etch out electrode array 14 and corresponding copper routing 34 to the connectors.
- the bottom copper layer 46 preferably comprises a crisscross ground plane to shield electrode array 14 from unwanted electromagnetic interference.
- the flex substrate 16 assembly comprises Pyralux FR material from Dupont.
- Pyralux FR material from Dupont.
- approximately 5 mil thick FR9150R double-sided Pyralux FR copper clad laminate is used as the Kapton substrate.
- Top coverlay 30 comprises Pyralux 5 mil FR0150 and the bottom coverlay 48 comprises 1 mil FR0110 Pyralux.
- the thickness of the top FR0150 coverlay 30 is an important parameter as it affects the sensitivity of sensing electrodes in measuring skin moisture content. Copper layers 44 , 46 are generally 1.4 mil thick, while adhesive layers 42 are generally 1 mil thick.
- the stiffener 50 is shown in FIG. 4 is approximately 31 mil thick.
- FIG. 5 shows a side view of a preferred alternative flex stack-up for a Kapton based substrate 120 , where thin adhesive layers 42 (1 mil) are used to attach an 18 mil Kapton layer 122 in between 1.4 mil copper layers 44 and 46 , all of which are disposed between 2 mil upper coverlay 30 and 1 mil lower coverlay 48 .
- a stiffener 50 is disposed under lower coverlay 48 , being positioned directly under copper layer 46 of the sensing pad.
- the 31 mil FR4 stiffener 126 forms a rigid portion of the substrate under the array 14 of sensing pads, connectors 66 and interfacing 34 .
- a 2 mil layer of PSA adhesive 124 is used between the bottom coverlay 48 and stiffener 126 .
- the layering of assembly 120 is configured to provide proper shielding from interference.
- FIG. 6 shows a top view of three separate and adjacently arranged concentric bipolar electrode sensing Kapton-based flex pads 60 , 70 and 80 having different sized capacitive sensing concentric electrodes.
- Pad 60 comprises a substrate having two large concentric electrodes 62 wired through substrate 64 via connectors 34 to lead line inputs 66 .
- Pad 70 comprises a substrate having two medium concentric electrodes 72 wired through substrate 74 to lead line inputs 76 .
- Pad 80 comprises a substrate having two small concentric electrodes 82 wired through substrate 84 to lead line inputs 86 .
- the configuration shown in FIG. 6 is optimized for cutting/manufacturing and also to avoid interference between data lines and sensors.
- Each of the bipolar electrode pads is individually wired to the electronics package 22 to allow for independent interrogation, excitation, and data retrieval.
- FIG. 7 illustrates an exploded perspective component view of the SEM scanner 10 .
- the silicone edge sealing gasket 18 is applied over the Kapton sensor substrate assembly 16 to seal and shield the edge interface connectors through which interface electronics package 22 excite and controls the sensing electrode array 14 .
- the Kapton sensor substrate assembly 16 rests on a conformal silicone pressure pad 12 that provides both support and conformity to enable measurements over body curvature and bony prominences.
- pressure sensor 11 may be embedded under each sensing electrode 24 , 26 (e.g. in an identical array not shown), sandwiched between Kapton sensor substrate 26 and the conformal silicone pressure pad 28 to measure applied pressure at each electrode, thus ensuring a uniform pressure and precise capacitance sensing.
- Lead access apertures 28 provide passage for routing the connector wires (not shown) from the substrate connectors (e.g. 66 , 76 , 86 ) through the pressure pad 12 , annular spacer 20 to the interface electronics 22 .
- the annular silicone spacer 20 comprises a central opening 27 that provides needed spacing between the conformal silicone pressure pad 12 and the interface electronics package 22 to allow the pressure pad 12 and flexible substrate to conform in a non-planar fashion to conduct measurements over body curvatures or bony prominences.
- the interface electronics package 22 is connected to a logging unit or other electronics (not shown) through wire-line USB connector 56 .
- the interface electronics package 22 preferably comprises an enclosure that contains all the electronics (not shown) needed to excite, program and control the sensing operation and manage the logged data.
- the electronics package 22 may also comprise Bluetooth or other wireless communication capabilities to allow for transfer of sensing data to a computer or other remote device. Docked data transfer is also contemplated, in addition to real-time Bluetooth transfer.
- a gateway device (not shown) may be used for communicating with the SEM device 10 and data formatting prior to upload to a computer or backend server.
- FIG. 8 is a schematic side view of the SEM scanner 10 in the nominal configuration, showing the edge gasket 18 over Kapton substrate 16 , and lead access apertures 28 , which provide access through annular spacer 20 and conformal pad 12 to electronics 22 .
- FIG. 9 illustrates a schematic side view of the SEM scanner 10 in contact with the target subject 25 .
- the annular silicone spacer 20 provides enough spacing for conforming silicone pad 12 to conform to the target surface 25 .
- the conforming silicone pad 12 enables continuous contact between the substrate 16 and patient’s skin 25 , thus minimizing gaps between the substrate 16 and patient’s skin 25 that could otherwise result in improper readings of the patient anatomy.
- Electrode array 14 which is embedded in substrate16, is shown interrogating into the derma of tissue 25 by directing emission of an RF signal or energy into the skin and receiving the signal and correspondingly reading the reflected signal.
- the interrogator or electronics package 22 excites electrode coil 14 by providing the needed energy burst to support the scanning/reading of the tissue.
- Each embedded electrode 14 measures the equivalent sub-epidermal capacitance corresponding to the moisture content of the target skin 25 .
- RF is generally preferred for its resolution in SEM scanning.
- FIG. 10 illustrates a perspective view of an assembled SEM scanner 10 with an alternative substrate 16b having an array 14 of ten sensors dispersed within the substrate 16b.
- This larger array 14 provides for a larger scanning area of the subject anatomy, thus providing a complete picture of the target anatomy in one image without having to generate a scanning motion. It is appreciated that array 14 may comprise any number of individual sensors, in be disposed in a variety of patterns.
- the SEM scanner 10 was evaluated using a number of different sized and types of sensors 26 .
- Table 1 illustrates electrode geometries are used throughout the following measurements.
- the outer ring electrode diameter D o varied from 5 mm for the XXS pad, to 55 mm for the large pad.
- the outer ring electrode inner diameter D i varied from 4 mm for the XXS pad, to 40 mm for the large pad.
- the inner electrode diameter D c varied from 2 mm for the XXS pad, to 7 mm for the large pad. It is appreciated that the actual dimensions of the electrodes may vary from ranges shown in these experiments.
- the contact diameter may range from 5 mm to 30 mm, and preferably ranges from 10 mm to 20 mm.
- FIG. 11 is a plot of normalized responses of the tested electrodes of the present invention.
- the four sensors’ (XXS, XS, S, M) normalized responses are compared in FIG. 11 and Table 2.
- the S electrode appears to be most responsive overall to the presence of moisture. Both the M and S electrodes seem to exhibit a peak. This suggests a depth dependency of the moisture being absorbed into the skin, as the roll-off from the M electrode occurs about 5 minutes after the peak for S electrode.
- the SEM scanner 10 was also tested on the inner arm.
- a resistive pressure sensor e.g. sensor 11 shown in FIG. 7
- the dry inner arm was measured using the XS, S and M electrodes. Then, the same area was masked off with tape, and moisturizer lotion was applied for 30 minutes. Subsequent measurements were made on the same location after cleaning the surface.
- FIG. 12 is a graph of measured equivalent capacitance for dry Volar arm for three different sized (M, S, XS) concentric sensor electrodes before applying the commercial lotion moisturizer.
- FIG. 13 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 30 minutes of applying lotion).
- FIG. 14 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 15 minutes of applying lotion) on two subjects. This experiment was performed with faster sampling intervals and with lotion applied for 15 minutes only on forearms of two test subjects. Again, a resistive pressure sensor was used to measure pressure applied on sensor to the arm. This way, constant pressure is applied across measurements. First the dry inner arm was measured using the XS, S and M electrodes. Then the same area was masked off with tape, and lotion was applied for 15 minutes. Subsequent measurements were made on the same location every 5 minutes. Pressure was maintained at 50 k Ohms, and the forearm was tested again.
- case “F” was compared to case “A” and also compared to previous measurements. Case “F” took a shower right before running the measurements and hence as a result his skin was relatively saturated with moisture. As a result, we observed less degree of sensitivity to the applied deep moisturizer for case “F”.
- FIG. 15 is a plot of results for fractional change vs. time for M, S and XS electrodes.
- FIG. 16 shows a preferred embodiment of a layered SEM scanner electrode system 100 having a first electrode pad 102 and second electrode pad 104 .
- Pad 104 is connected to lead line inputs 116 via wiring 34 along curved path 112 .
- Pad 102 is connected to lead line inputs 110 via wiring 34 along curved path 106 .
- a stiffener layer e.g. layer 126 in FIG. 5 ) is provided directly under lead inputs 110 and 116 (see footprint 108 and 114 respectively) and under pads 102 and 104 (see footprint 122 and 120 respectively).
- the electrode size is approximately 2300 in width by 3910 mil in height.
- FIG. 17 illustrates the SEM Scanner mechanical compliance (forcedisplacement relationship) for electrodes of system 100 , developed to enable probing of bony prominence.
- the diamond symbols show the upper electrode 104 response, square symbols show the lower electrode 102 response.
- the SEM scanner device 10 may also include other instruments, such as a camera (not shown), which can be used to take pictures of the wound, or develop a scanning system to scan barcodes as a login mechanism or an interrogator.
- a camera not shown
- the SEM scanner device 10 may also include other instruments, such as a camera (not shown), which can be used to take pictures of the wound, or develop a scanning system to scan barcodes as a login mechanism or an interrogator.
- Patients using the SEM scanner device 10 may wear a bracelet (not shown) that contains data relating to their patient ID. This ID can be scanned by the camera embedded in the SEM scanner 10 to confirm correct patient ID correspondence. Alternatively, a separate RF scanner (not shown) may be used for interrogating the bracelet (in addition to the camera).
- the SEM scanner device 10 is preferably ergonomically shaped to encourage correct placement of the device on desired body location.
- the SEM Scanner device 10 of the present invention is capable of generating physical, absolute measurement values, and can produce measurements at multiple depths.
- FIG. 18 shows the mapping function used to transform the target image.
- wound images are obtained from a smart patch, which is able to retrieve multiple types of images from the same wound scan, including a moisture map and a pressure map of the bony prominence. This is summarized in FIG. 19 .
- FIG. 19 demonstrates how both pressure and moisture measurements are obtained from the wound. This enables the registration of two different readings, obtained on two different days as shown in FIG. 20 .
- the left column shows the reading, including pressure and moisture, from day 1 and the right column shows the reading from day 2. Note the images obtained are severely misaligned.
- An apparatus for sensing sub-epidermal moisture from a location external to a patient’s skin comprising: a bipolar RF sensor embedded on a flexible substrate; a conformal pressure pad disposed adjacent and underneath the substrate; wherein the conformal pressure pad is configured to support the flexible substrate while allowing the flexible substrate to conform to a non-planar sensing surface of the patient’s skin; and interface electronics coupled to the sensor; wherein said interface electronics is configured to control emission and reception of RF energy to interrogate the patient’s skin.
- each of the sensors is configured to measure an equivalent sub-epidermal capacitance of a target region of skin; said sub-epidermal capacitance corresponding to the moisture content of the target region of skin.
- the array of sensors comprises a first sensor having a first contact area and a second sensor having a second contact area larger than the first sensor; wherein the first and second sensors interrogate the skin at different depths.
- the substrate comprises a substrate assembly comprising a substrate layer; and wherein the sensor comprises a sensing pad having a first electrode embedded on a first side of the substrate and a second electrode embedded on a second side of the substrate.
- said first electrode comprises an annular ring having an inner radius and an outer radius
- said second electrode comprises an outer radius having a smaller diameter than the inner radius of the first electrode; and wherein said second electrode is concentric with said first radius.
- invention 4 further comprising: a pressure sensor positioned in line with said RF sensor; said pressure sensor configured to measure an applied pressure of the substrate at a location on the patient’s skin.
- a scanner for sensing sub-epidermal moisture from a location external to a patient’s skin comprising: an array of bipolar RF sensors embedded on a flexible substrate; and a conformal pressure pad disposed adjacent and underneath the substrate; wherein the conformal pressure pad is configured to support the flexible substrate while allowing the flexible substrate to conform to a non-planar sensing surface of the patient’s skin; wherein said sensor array is configured to emit and receive RF energy to interrogate the patient’s skin; and wherein each of the sensors are independently are individually wired to independently interrogate the patient’s skin.
- each of the sensors is configured to measure an equivalent sub-epidermal capacitance of a target region of skin; said sub-epidermal capacitance corresponding to the moisture content of the target region of skin.
- the array of sensors comprises a first sensor having a first contact area and a second sensor having a second contact area larger than the first sensor; and wherein the first and second sensors interrogate the skin at different depths.
- each sensor comprises a first electrode in the form of an annular ring having an inner radius and an outer radius and a second electrode comprising an outer radius having a smaller diameter than the first electrode; and wherein said second electrode is concentric with said first radius.
- the substrate comprises a substrate assembly comprising a substrate layer; and wherein the first electrode is embedded on a first side of the substrate and the second electrode embedded on a second side of the substrate.
- a method for monitoring the formation of pressure ulcers at a target location of a patient’s skin comprising: positioning a flexible substrate adjacent the target location of the patient’s skin; the flexible substrate comprising one or more bipolar RF sensors; conforming the flexible substrate to the patient’s skin at the target location; exciting the one or more bipolar RF sensor to emit RF energy into the patient’s skin; and measuring the capacitance of the skin at the target location as an indicator of the Sub-Epidermal Moisture (SEM) at the target location.
- SEM Sub-Epidermal Moisture
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- General Health & Medical Sciences (AREA)
- Veterinary Medicine (AREA)
- Biophysics (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- Physics & Mathematics (AREA)
- Public Health (AREA)
- Pathology (AREA)
- Dermatology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Artificial Intelligence (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Physiology (AREA)
- Psychiatry (AREA)
- Signal Processing (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
- Investigating Or Analyzing Materials By The Use Of Electric Means (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
Description
- This application is a continuation of U.S. Pat. Application No. 16/440,687 filed Jun. 13, 2019, which is a continuation of U.S. Pat. Application No. 16/210,911 filed on Dec. 5, 2018 (now U.S. Pat. No. 11,253,192 which issued on Feb. 22, 2022), which is a continuation of U.S. Pat. Application No. 15/095,046 filed on Apr. 9, 2016 (now U.S. Pat. No. 10,188,340 which issued on Jan. 29, 2019), which is a continuation of U.S. Pat. Application No. 15/058,964 filed on Mar. 2, 2016 (now U.S. Pat. No. 9,980,673 which issued on May 29, 2018), which is a continuation of U.S. Pat. Application No. 14/827,375 filed on Aug. 17, 2015 (now U.S. Pat. No. 9,398,879 which issued on Jul. 26, 2016), which is a continuation of U.S. Pat. Application No. 14/297,977 filed on Jun. 6, 2014 (now U.S. Pat. No. 9,220,455 which issued on Dec. 29, 2015), which is a continuation of U.S. Pat. Application No. 13/668,047 filed on Nov. 2, 2012 (which is abandoned), which is a 35 U.S.C. § 111(a) continuation of International Application No. PCT/US2011/035618 filed on May 6, 2011, which claims the benefit of U.S. Provisional Application No. 61/332,755 filed on May 8, 2010, and claims the benefit of U.S. Provisional Application No. 61/453,852 filed Mar. 17, 2011, all of which are hereby incorporated by reference herein.
- The above-referenced PCT international application was published as PCT International Publication No. WO 2011/143071 on Nov. 17, 2011 and republished on Apr. 5, 2012, and is incorporated herein by reference in its entirety.
- Not Applicable
- Not Applicable
- A portion of the material in this patent document is subject to copyright protection under the copyright laws of the United States and of other countries. The owner of the copyright rights has no objection to the facsimile reproduction by anyone of the patent document or the patent disclosure, as it appears in the United States Patent and Trademark Office publicly available file or records, but otherwise reserves all copyright rights whatsoever. The copyright owner does not hereby waive any of its rights to have this patent document maintained in secrecy, including without limitation its rights pursuant to 37 C.F.R. § 1.14.
- This invention pertains generally to monitoring skin pressure ulcers and more particularly to skin ulcer monitoring via measurement of Sub-epidermal Moisture (SEM).
- Patients’ skin integrity has long been an issue of concern for nurses and in nursing homes. Maintenance of skin integrity has been identified by the American Nurses Association as an important indicator of quality nursing care. Meanwhile, pressure ulcers remain a major health problem particularly for hospitalized older adults. When age is considered along with other risk factors, the incidence of pressure ulcers is significantly increased. Overall incidence of pressure ulcers for hospitalized patients ranges from 2.7% to 29.5%, and rates of greater than 50% have been reported for patients in intensive care settings. In a multicenter cohort retrospective study of 1,803 older adults discharged from acute care hospitals with selected diagnoses, 13.2% (i.e., 164 patients) demonstrated an incidence of stage I ulcers. Of those 164 patients, 38 (16%) had ulcers that progressed to a more advanced stage. Pressure ulcers additionally have been associated with an increased risk of death one year after hospital discharge. The estimated cost of treating pressure ulcers ranges from $5,000 to $40,000 for each ulcer, depending on severity.
- Therefore, there is an urgent need to develop a preventive solution to measure moisture content of the skin as a mean to detect early symptoms of ulcer development.
- An aspect of the present invention is a smart compact capacitive sensing conforming handheld apparatus configured to measure Sub-epidermal Moisture (SEM) as a mean to detect and monitor the development of pressure ulcers. The device incorporates an array of electrodes which are excited to measure and scan SEM in a programmable and multiplexed manner by a battery-less RF-powered chip. The scanning operation is initiated by an interrogator which excites a coil embedded in the apparatus and provides the needed energy burst to support the scanning/reading operation. Each embedded electrode measures the equivalent sub-epidermal capacitance corresponding and representing the moisture content of the target surface.
- An aspect of this invention is the in situ sensing and monitoring of skin or wound or ulcer development status using a wireless, biocompatible RF powered capacitive sensing system referred to as smart SEM imager. The present invention enables the realization of smart preventive measures by enabling early detection of ulcer formation or inflammatory pressure which would otherwise have not been detected for an extended period with increased risk of infection and higher stage ulcer development.
- In one beneficial embodiment, the handheld capacitive sensing imager apparatus incorporates pressure sensing components in conjunction with the sensing electrodes to monitor the level of applied pressure on each electrode in order to guarantee precise wound or skin electrical capacitance measurements to characterize moisture content. In summary, such embodiment would enable new capabilities including but not limited to: 1) measurement capabilities such as SEM imaging and SEM depth imaging determined by electrode geometry and dielectrics, and 2) signal processing and pattern recognition having automatic and assured registration exploiting pressure imaging and automatic assurance of usage exploiting software systems providing usage tracking.
- One major implication of this sensor-enhanced paradigm is the ability to better manage each individual patient resulting in a timelier and more efficient practice in hospitals and even nursing homes. This is applicable to patients with a history of chronic wounds, diabetic foot ulcers, pressure ulcers or post-operative wounds. In addition, alterations in signal content may be integrated with the activity level of the patient, the position of patient’s body and standardized assessments of symptoms. By maintaining the data collected in these patients in a signal database, pattern classification, search, and pattern matching algorithms can be developed to better map symptoms with alterations in skin characteristics and ulcer development. This approach is not limited to the specific condition of ulcer or wound, but may have broad application in all forms of wound management and even skin diseases or treatments.
- One aspect is apparatus for sensing sub-epidermal moisture (SEM) from a location external to a patient’s skin. The apparatus includes a bipolar RF sensor embedded on a flexible substrate, and a conformal pressure pad disposed adjacent and underneath the substrate, wherein the conformal pressure pad is configured to support the flexible substrate while allowing the flexible substrate to conform to a non-planar sensing surface of the patient’s skin. The apparatus further includes interface electronics coupled to the sensor; wherein the interface electronics are configured to control emission and reception of RF energy to interrogate the patient’s skin.
- Another aspect is a method for monitoring the formation of pressure ulcers at a target location of a patient’s skin. The method includes the steps of positioning a flexible substrate adjacent the target location of the patient’s skin; the flexible substrate comprising one or more bipolar RF sensors; conforming the flexible substrate to the patient’s skin at the target location; exciting the one or more bipolar RF sensor to emit RF energy into the patient’s skin; and measuring the capacitance of the skin at the target location as an indicator of the Sub-Epidermal Moisture (SEM) at the target location.
- Further aspects of the invention will be brought out in the following portions of the specification, wherein the detailed description is for the purpose of fully disclosing preferred embodiments of the invention without placing limitations thereon.
- The invention will be more fully understood by reference to the following drawings which are for illustrative purposes only:
-
FIG. 1 illustrates an assembled perspective component view of the SEM Scanner of the present invention. -
FIG. 2 illustrates a perspective view of a Kapton-based conforming sensing substrate assembly of the present invention. -
FIG. 3 shows a top view of an exemplary concentric sensing electrode in accordance with the present invention. -
FIG. 4 illustrates a side view of a flex stack-up for the Kapton-based conforming sensing substrate shown inFIG. 2 . -
FIG. 5 illustrates a side view of an alternative flex stack-up for a Kapton-based conforming sensing substrate. -
FIG. 6 shows a top view of two-electrode sensing Kapton-based flex sensor substrates for three alternative types of capacitive sensing concentric electrodes. -
FIG. 7 illustrates an exploded perspective component view of the SEM scanner ofFIG. 1 . -
FIG. 8 illustrates a schematic side view of the SEM scanner ofFIG. 1 . -
FIG. 9 illustrates a schematic side view of the SEM scanner ofFIG. 8 in contact with subject skin. -
FIG. 10 illustrates a perspective view of an assembled SEM scanner with an alternative array of sensors in accordance with the present invention. -
FIG. 11 is a plot of normalized responses of the tested electrodes of the present invention. -
FIG. 12 is a graph of measured equivalent capacitance for dry volar arm for three different concentric sensor electrodes. -
FIG. 13 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 30 minutes of applying lotion). -
FIG. 14 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 15 minutes of applying lotion). -
FIG. 15 is a plot of fractional change vs. time. -
FIG. 16 shows a SEM scanner electrode system and electrode layering providing proper shielding from interference. -
FIG. 17 shows an SEM scanner mechanical compliance for electrodes developed to enable probing of bony prominence. -
FIG. 18 is an overview of the wound registration method according to an embodiment of the description. -
FIG. 19 illustrates pressure and moisture measurements obtained according to an embodiment of the description. -
FIG. 20 illustrates sample measurements over two different days. - In one exemplary embodiment, a smart handheld capacitive sensing device according to the present invention employs a programmable sensing electrode array. This is based on methods that use an interrogator to excite the embedded electrodes.
-
FIG. 1 andFIG. 7 illustrate an SEM scanning/sensing apparatus 10 according to the present invention. Theapparatus 10 comprises five main components, including a top siliconeedge sealing gasket 18 encircling a Kapton-basedsensing substrate 16, which rests on a conformalsilicone pressure pad 12. A thickannular silicone spacer 20 is disposed under the pressure pad to provide free space for the pressure pad to deform. The bottom layer comprises an interfaceelectronics package enclosure 22 that houses interface circuitry for interrogating and transmitting data for evaluation. These five main components are described in further detail below. - In the embodiment shown in
FIG. 1 , anarray 14 of individualRF electrode sensors biocompatible substrate 16.Substrate 16 may comprise a laminated Kapton (Polyimide) chip-on-flex. -
FIG. 2 illustrates one embodiment of aKapton sensor substrate 16a that comprises anarray 14 of differing sized concentric sensing electrodes. A flexible biocompatible Polyimide orKapton substrate 32 comprises a layer of sensing electrodes coated on one side with an ultrathin cover layer 30 of Polyimide (e.g. CA335) to isolate the electrodes from direct moisture contact and also to provide a uniform contact surface. - In
FIG. 2 , sample capacitive sensing electrodes of different sizes (e.g. 24, 26, and 29) are shown in anarray 14, and which are manipulated to achieve and sense different depths of skin. The array ofsensing electrodes 14 may comprise any number of different shape and configurations, such as theconcentric circles sensor 15. -
FIG. 3 illustrates a close-up top view of aconcentric sensing pad 26 in accordance with the present invention.Pad 26 comprises a bipolar configuration having afirst electrode 36 comprising an outer annular ring disposed around a second innercircular electrode 38.Outer ring electrode 36 has an outer diameter Do and an inner diameter Di that is larger than the diameter Dc of the circularinner electrode 38 to formannular gap 40. Innercircular electrode 38 andouter ring electrode 36 are coupled electrically to interface electronics in theinterface electronics package 22. As shown in greater detail inFIGS. 4 and 5 ,electrodes substrate assembly 16. - The dimensions of the
sensor pads e.g. pad 26 or 29) will penetrate deeper into the skin than a smaller pad. The desired depth may vary depending on the region of the body being scanned, or the age, skin anatomy or other characteristic of the patient. Thus,SEM scanner 10 may comprise an array of different sized pads (e.g.small pads 24 and mediumsized pads 26 shown inFIG. 1 ) each individually coupled to theinterface electronics package 22. -
FIG. 4 illustrates side view of a flex stack-up for a Kapton basedsubstrate assembly 16, where thinadhesive layers 42 are used to attach aKapton layer 32 in betweencopper layers lower coverlay 48. Astiffener 50 is disposed underlower coverlay 48, being positioned directly undercopper layer 46 of the sensing pads. Thestiffener 50 forms a rigid portion of the substrate wheresensing pad array 14, connectors (e.g. connectors FIG. 6 ) and interfacing (e.g. lead wires 34) are located, so that these areas do not deform, whereas the rest of the substrate is free to deform. Thetop copper layer 44 is used to etch outelectrode array 14 andcorresponding copper routing 34 to the connectors. Thebottom copper layer 46 preferably comprises a crisscross ground plane to shieldelectrode array 14 from unwanted electromagnetic interference. - In one embodiment, the
flex substrate 16 assembly comprises Pyralux FR material from Dupont. In an exemplary configuration, approximately 5 mil thick FR9150R double-sided Pyralux FR copper clad laminate is used as the Kapton substrate.Top coverlay 30 comprisesPyralux 5 mil FR0150 and thebottom coverlay 48 comprises 1 mil FR0110 Pyralux. The thickness of thetop FR0150 coverlay 30 is an important parameter as it affects the sensitivity of sensing electrodes in measuring skin moisture content. Copper layers 44, 46 are generally 1.4 mil thick, whileadhesive layers 42 are generally 1 mil thick. Thestiffener 50 is shown inFIG. 4 is approximately 31 mil thick. -
FIG. 5 shows a side view of a preferred alternative flex stack-up for a Kapton basedsubstrate 120, where thin adhesive layers 42 (1 mil) are used to attach an 18mil Kapton layer 122 in between 1.4 mil copper layers 44 and 46, all of which are disposed between 2 milupper coverlay lower coverlay 48. Astiffener 50 is disposed underlower coverlay 48, being positioned directly undercopper layer 46 of the sensing pad. The 31mil FR4 stiffener 126 forms a rigid portion of the substrate under thearray 14 of sensing pads,connectors 66 and interfacing 34. A 2 mil layer of PSA adhesive 124 is used between thebottom coverlay 48 andstiffener 126. The layering ofassembly 120 is configured to provide proper shielding from interference. -
FIG. 6 shows a top view of three separate and adjacently arranged concentric bipolar electrode sensing Kapton-basedflex pads Pad 60 comprises a substrate having two largeconcentric electrodes 62 wired throughsubstrate 64 viaconnectors 34 to leadline inputs 66.Pad 70 comprises a substrate having two mediumconcentric electrodes 72 wired throughsubstrate 74 to leadline inputs 76.Pad 80 comprises a substrate having two smallconcentric electrodes 82 wired throughsubstrate 84 to leadline inputs 86. The configuration shown inFIG. 6 is optimized for cutting/manufacturing and also to avoid interference between data lines and sensors. Each of the bipolar electrode pads is individually wired to theelectronics package 22 to allow for independent interrogation, excitation, and data retrieval. -
FIG. 7 illustrates an exploded perspective component view of theSEM scanner 10. The siliconeedge sealing gasket 18 is applied over the Kaptonsensor substrate assembly 16 to seal and shield the edge interface connectors through whichinterface electronics package 22 excite and controls thesensing electrode array 14. The Kaptonsensor substrate assembly 16 rests on a conformalsilicone pressure pad 12 that provides both support and conformity to enable measurements over body curvature and bony prominences. - In one beneficial embodiment,
pressure sensor 11 may be embedded under each sensingelectrode 24, 26 (e.g. in an identical array not shown), sandwiched betweenKapton sensor substrate 26 and the conformalsilicone pressure pad 28 to measure applied pressure at each electrode, thus ensuring a uniform pressure and precise capacitance sensing. - Lead
access apertures 28 provide passage for routing the connector wires (not shown) from the substrate connectors (e.g. 66, 76, 86) through thepressure pad 12,annular spacer 20 to theinterface electronics 22. - The
annular silicone spacer 20 comprises acentral opening 27 that provides needed spacing between the conformalsilicone pressure pad 12 and theinterface electronics package 22 to allow thepressure pad 12 and flexible substrate to conform in a non-planar fashion to conduct measurements over body curvatures or bony prominences. - In one embodiment, the
interface electronics package 22 is connected to a logging unit or other electronics (not shown) through wire-line USB connector 56. - The
interface electronics package 22 preferably comprises an enclosure that contains all the electronics (not shown) needed to excite, program and control the sensing operation and manage the logged data. Theelectronics package 22 may also comprise Bluetooth or other wireless communication capabilities to allow for transfer of sensing data to a computer or other remote device. Docked data transfer is also contemplated, in addition to real-time Bluetooth transfer. A gateway device (not shown) may be used for communicating with theSEM device 10 and data formatting prior to upload to a computer or backend server. -
FIG. 8 is a schematic side view of theSEM scanner 10 in the nominal configuration, showing theedge gasket 18 overKapton substrate 16, andlead access apertures 28, which provide access throughannular spacer 20 andconformal pad 12 toelectronics 22. -
FIG. 9 illustrates a schematic side view of theSEM scanner 10 in contact with thetarget subject 25. Theannular silicone spacer 20 provides enough spacing for conformingsilicone pad 12 to conform to thetarget surface 25. The conformingsilicone pad 12 enables continuous contact between thesubstrate 16 and patient’sskin 25, thus minimizing gaps between thesubstrate 16 and patient’sskin 25 that could otherwise result in improper readings of the patient anatomy.Electrode array 14, which is embedded in substrate16, is shown interrogating into the derma oftissue 25 by directing emission of an RF signal or energy into the skin and receiving the signal and correspondingly reading the reflected signal. The interrogator orelectronics package 22 exciteselectrode coil 14 by providing the needed energy burst to support the scanning/reading of the tissue. Each embeddedelectrode 14 measures the equivalent sub-epidermal capacitance corresponding to the moisture content of thetarget skin 25. - While other energy modalities are contemplated (e.g. ultrasound, microwave, etc.), RF is generally preferred for its resolution in SEM scanning.
-
FIG. 10 illustrates a perspective view of an assembledSEM scanner 10 with analternative substrate 16b having anarray 14 of ten sensors dispersed within thesubstrate 16b. Thislarger array 14 provides for a larger scanning area of the subject anatomy, thus providing a complete picture of the target anatomy in one image without having to generate a scanning motion. It is appreciated thatarray 14 may comprise any number of individual sensors, in be disposed in a variety of patterns. - The
SEM scanner 10 was evaluated using a number of different sized and types ofsensors 26. Table 1 illustrates electrode geometries are used throughout the following measurements. As shown inFIG. 1 the outer ring electrode diameter Do varied from 5 mm for the XXS pad, to 55 mm for the large pad. The outer ring electrode inner diameter Di varied from 4 mm for the XXS pad, to 40 mm for the large pad. The inner electrode diameter Dc varied from 2 mm for the XXS pad, to 7 mm for the large pad. It is appreciated that the actual dimensions of the electrodes may vary from ranges shown in these experiments. For example, the contact diameter may range from 5 mm to 30 mm, and preferably ranges from 10 mm to 20 mm. - To measure the properties of each sensor size listed in Table 1, the sensors were fabricated using both Kapton and rigid board. In testing with the rigid sensor pads, lotion was applied to the thumb continuously for 15 minutes.
-
FIG. 11 is a plot of normalized responses of the tested electrodes of the present invention. The four sensors’ (XXS, XS, S, M) normalized responses are compared inFIG. 11 and Table 2. - As can be seen in
FIG. 11 and Table 2, the S electrode appears to be most responsive overall to the presence of moisture. Both the M and S electrodes seem to exhibit a peak. This suggests a depth dependency of the moisture being absorbed into the skin, as the roll-off from the M electrode occurs about 5 minutes after the peak for S electrode. - The
SEM scanner 10 was also tested on the inner arm. A resistive pressure sensor (e.g. sensor 11 shown inFIG. 7 ) was also used to measure pressure applied on sensor to the arm. This way, constant pressure is applied across measurements. First, the dry inner arm was measured using the XS, S and M electrodes. Then, the same area was masked off with tape, and moisturizer lotion was applied for 30 minutes. Subsequent measurements were made on the same location after cleaning the surface. -
FIG. 12 is a graph of measured equivalent capacitance for dry Volar arm for three different sized (M, S, XS) concentric sensor electrodes before applying the commercial lotion moisturizer. -
FIG. 13 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 30 minutes of applying lotion). -
FIG. 14 is a plot of time dependent fractional change in capacitance relative to dry skin for three different concentric sensor electrodes (after 15 minutes of applying lotion) on two subjects. This experiment was performed with faster sampling intervals and with lotion applied for 15 minutes only on forearms of two test subjects. Again, a resistive pressure sensor was used to measure pressure applied on sensor to the arm. This way, constant pressure is applied across measurements. First the dry inner arm was measured using the XS, S and M electrodes. Then the same area was masked off with tape, and lotion was applied for 15 minutes. Subsequent measurements were made on the same location every 5 minutes. Pressure was maintained at 50 k Ohms, and the forearm was tested again. We noticed an interesting observation for the case “F” in comparison to case “A” and also compared to previous measurements. Case “F” took a shower right before running the measurements and hence as a result his skin was relatively saturated with moisture. As a result, we observed less degree of sensitivity to the applied deep moisturizer for case “F”. - The experiment was performed again for case “F”, with a time resolution of 3 minutes, knowing that the subject did not shower in the morning before the test. The lotion was applied to the inner forearm for 15 minutes. Pressure was maintained at 50 k Ohms. The results confirm the sensitivity of the measurement to the residual skin moisture.
-
FIG. 15 is a plot of results for fractional change vs. time for M, S and XS electrodes. -
FIG. 16 shows a preferred embodiment of a layered SEMscanner electrode system 100 having afirst electrode pad 102 andsecond electrode pad 104.Pad 104 is connected to leadline inputs 116 viawiring 34 alongcurved path 112.Pad 102 is connected to leadline inputs 110 viawiring 34 alongcurved path 106. A stiffener layer (e.g. layer 126 inFIG. 5 ) is provided directly underlead inputs 110 and 116 (seefootprint pads 102 and 104 (seefootprint - In this embodiment, the electrode size is approximately 2300 in width by 3910 mil in height.
-
FIG. 17 illustrates the SEM Scanner mechanical compliance (forcedisplacement relationship) for electrodes ofsystem 100, developed to enable probing of bony prominence. The diamond symbols show theupper electrode 104 response, square symbols show thelower electrode 102 response. - The
SEM scanner device 10 may also include other instruments, such as a camera (not shown), which can be used to take pictures of the wound, or develop a scanning system to scan barcodes as a login mechanism or an interrogator. - Patients using the
SEM scanner device 10 may wear a bracelet (not shown) that contains data relating to their patient ID. This ID can be scanned by the camera embedded in theSEM scanner 10 to confirm correct patient ID correspondence. Alternatively, a separate RF scanner (not shown) may be used for interrogating the bracelet (in addition to the camera). - The
SEM scanner device 10 is preferably ergonomically shaped to encourage correct placement of the device on desired body location. - The
SEM Scanner device 10 of the present invention is capable of generating physical, absolute measurement values, and can produce measurements at multiple depths. -
FIG. 18 shows the mapping function used to transform the target image. - In one embodiment of the description, wound images are obtained from a smart patch, which is able to retrieve multiple types of images from the same wound scan, including a moisture map and a pressure map of the bony prominence. This is summarized in
FIG. 19 . - Note the difference in our registration method from the previous work is that the two images can be significantly different from each other, due to the changes in wound healing. Additionally, we are aided from pressure readings obtained from the smart patch, which allow the improved registration of the more pertinent moisture maps. Bony prominence can be used in the feature detection phase.
-
FIG. 19 demonstrates how both pressure and moisture measurements are obtained from the wound. This enables the registration of two different readings, obtained on two different days as shown inFIG. 20 . The left column shows the reading, including pressure and moisture, fromday 1 and the right column shows the reading fromday 2. Note the images obtained are severely misaligned. - From the foregoing it will be appreciated that the present invention can be embodied in various ways, which include but are not limited to the following:
- 1. An apparatus for sensing sub-epidermal moisture from a location external to a patient’s skin, comprising: a bipolar RF sensor embedded on a flexible substrate; a conformal pressure pad disposed adjacent and underneath the substrate; wherein the conformal pressure pad is configured to support the flexible substrate while allowing the flexible substrate to conform to a non-planar sensing surface of the patient’s skin; and interface electronics coupled to the sensor; wherein said interface electronics is configured to control emission and reception of RF energy to interrogate the patient’s skin.
- 2. The apparatus of
embodiment 1, further comprising: an annular spacer adjacent and underneath the conformal pressure pad; wherein the annular spacer comprises a central opening configured to allow the conformal pressure pad to deflect freely into the central opening. - 3. The apparatus of
embodiment 1, further comprising: an array of bipolar RF sensors spaced across the flexible substrate; wherein each of the sensors is independently coupled to the interface electronics to independently interrogate the patient’s skin. - 4. The apparatus of embodiment 3: wherein each of the sensors is configured to measure an equivalent sub-epidermal capacitance of a target region of skin; said sub-epidermal capacitance corresponding to the moisture content of the target region of skin.
- 5. The apparatus of embodiment 4: wherein the array of sensors comprises a first sensor having a first contact area and a second sensor having a second contact area larger than the first sensor; wherein the first and second sensors interrogate the skin at different depths.
- 6. The apparatus of embodiment 4: wherein the substrate comprises a substrate assembly comprising a substrate layer; and wherein the sensor comprises a sensing pad having a first electrode embedded on a first side of the substrate and a second electrode embedded on a second side of the substrate.
- 7. The apparatus of
embodiment 6, further comprising a biocompatible cover layer disposed over said first side of said substrate layer. - 8. The apparatus of
embodiment 6, further comprising a cover layer disposed under said second side of said substrate layer. - 9. The apparatus of
embodiment 6, further comprising a stiffener layer disposed under said second side of said substrate layer; wherein the stiffener layer comprises a footprint substantially similar to that of the sensor array. - 10. The apparatus of embodiment 6: wherein said first electrode comprises an annular ring having an inner radius and an outer radius; wherein said second electrode comprises an outer radius having a smaller diameter than the inner radius of the first electrode; and wherein said second electrode is concentric with said first radius.
- 11. The apparatus of
embodiment 1, wherein the interface electronics are configured to transmit data retrieved from said sensors. - 12. The apparatus of embodiment 4, further comprising: a pressure sensor positioned in line with said RF sensor; said pressure sensor configured to measure an applied pressure of the substrate at a location on the patient’s skin.
- 13. The apparatus of
embodiment 1, wherein the flexible substrate comprises Kapton or Polyimide. - 14. A scanner for sensing sub-epidermal moisture from a location external to a patient’s skin, comprising: an array of bipolar RF sensors embedded on a flexible substrate; and a conformal pressure pad disposed adjacent and underneath the substrate; wherein the conformal pressure pad is configured to support the flexible substrate while allowing the flexible substrate to conform to a non-planar sensing surface of the patient’s skin; wherein said sensor array is configured to emit and receive RF energy to interrogate the patient’s skin; and wherein each of the sensors are independently are individually wired to independently interrogate the patient’s skin.
- 15. The scanner of
embodiment 14, further comprising: interface electronics coupled to the sensor; wherein said interface electronics is configured to control the emission and reception of RF energy. - 16. The scanner of
embodiment 14, further comprising: an annular spacer adjacent and underneath the conformal pressure pad; wherein the annular spacer comprises a central opening configured to allow the conformal pressure pad to deflect freely into the central opening. - 17. The scanner of embodiment 14: wherein each of the sensors is configured to measure an equivalent sub-epidermal capacitance of a target region of skin; said sub-epidermal capacitance corresponding to the moisture content of the target region of skin.
- 18. The scanner of embodiment 14: wherein the array of sensors comprises a first sensor having a first contact area and a second sensor having a second contact area larger than the first sensor; and wherein the first and second sensors interrogate the skin at different depths.
- 19. The scanner of embodiment 14: wherein each sensor comprises a first electrode in the form of an annular ring having an inner radius and an outer radius and a second electrode comprising an outer radius having a smaller diameter than the first electrode; and wherein said second electrode is concentric with said first radius.
- 20. The scanner of embodiment 19: wherein the substrate comprises a substrate assembly comprising a substrate layer; and wherein the first electrode is embedded on a first side of the substrate and the second electrode embedded on a second side of the substrate.
- 21. The scanner of
embodiment 20, further comprising: an upper biocompatible cover layer disposed over said first side of said substrate layer and a lower cover layer disposed under said second side of said substrate layer. - 22. The scanner of
embodiment 20, further comprising: a stiffener layer disposed under said second side of said substrate layer; wherein the stiffener layer comprises a footprint substantially similar to that of the sensor array. - 23. The scanner of
embodiment 14, further comprising: an array of pressure sensors positioned in line with said RF sensor; said pressure sensors are configured to measure an applied pressure of the substrate at corresponding locations on the patient’s skin. - 24. A method for monitoring the formation of pressure ulcers at a target location of a patient’s skin, comprising: positioning a flexible substrate adjacent the target location of the patient’s skin; the flexible substrate comprising one or more bipolar RF sensors; conforming the flexible substrate to the patient’s skin at the target location; exciting the one or more bipolar RF sensor to emit RF energy into the patient’s skin; and measuring the capacitance of the skin at the target location as an indicator of the Sub-Epidermal Moisture (SEM) at the target location.
- 25. The method of embodiment 24: wherein the one or more sensors comprise an array of sensors disposed across said substrate; and wherein the one or more sensors are individually controlled to independently excite the one or more sensors.
- 26. The method of
embodiment 24, further comprising: measuring an applied pressure of the substrate at the target location on the patient’s skin. - 27. The method of
embodiment 25, further comprising: measuring an applied pressure of the substrate on the patient’s skin at each of the sensors in the array. - Although the description above contains many details, these should not be construed as limiting the scope of the invention but as merely providing illustrations of some of the presently preferred embodiments of this invention. Therefore, it will be appreciated that the scope of the present invention fully encompasses other embodiments which may become obvious to those skilled in the art, and that the scope of the present invention is accordingly to be limited by nothing other than the appended claims, in which reference to an element in the singular is not intended to mean “one and only one” unless explicitly so stated, but rather “one or more.” All structural, chemical, and functional equivalents to the elements of the above-described preferred embodiment that are known to those of ordinary skill in the art are expressly incorporated herein by reference and are intended to be encompassed by the present claims. Moreover, it is not necessary for a device or method to address each and every problem sought to be solved by the present invention, for it to be encompassed by the present claims. Furthermore, no element, component, or method step in the present disclosure is intended to be dedicated to the public regardless of whether the element, component, or method step is explicitly recited in the claims. No claim element herein is to be construed as a “means plus function” element unless the element is expressly recited using the phrase “means for”. No claim element herein is to be construed as a “step plus function” element unless the element is expressly recited using the phrase “step for”.
-
TABLE 1 Symbol XXS XS S M L Contact Diameter (mm) 5 10 20 23 55 Approx Outer Do (mm) 5 10 20 23 55 Approx Middle Di (mm) 4 6 10 15 40 Approx Inner Dc (mm) 2 2 4 5 7 -
TABLE 2 Tabulated Normalized Responses of M, S, XS and XXS Electrodes Time M M Baseline S S Baseline XS XS Baseline XXS XXS Baseline 0 2.32 2.04 1.89 1.5 0.261 0.24 1.12 1.04 5 2.32 2.04 1.9 1.5 0.256 0.24 1.1 1.04 10 2.38 2.04 1.92 1.5 0.259 0.24 1.07 1.04 15 2.4 2.04 1.99 1.5 0.255 0.24 1.06 1.04 20 2.39 2.04 1.93 1.5 0.248 0.24 1.05 1.04 25 2.25 2.04 1.92 1.5 0.25 0.24 1.04 1.04 30 2.21 2.04 1.88 1.5 0.248 0.24 1.04 1.04 35 2.18 2.04 1.86 1.5 0.245 0.24 1.04 1.04
Claims (31)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US18/346,103 US20230337966A1 (en) | 2010-05-08 | 2023-06-30 | SEM Scanner Sensing Apparatus, System and Methodology for Early Detection of Ulcers |
Applications Claiming Priority (11)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US33275510P | 2010-05-08 | 2010-05-08 | |
US201161453852P | 2011-03-17 | 2011-03-17 | |
PCT/US2011/035618 WO2011143071A2 (en) | 2010-05-08 | 2011-05-06 | Sem scanner sensing apparatus, system and methodology for early detection of ulcers |
US13/668,047 US20130123587A1 (en) | 2010-05-08 | 2012-11-02 | Sem scanner sensing apparatus, system and methodology for early detection of ulcers |
US14/297,977 US9220455B2 (en) | 2010-05-08 | 2014-06-06 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US14/827,375 US9398879B2 (en) | 2010-05-08 | 2015-08-17 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US15/058,964 US9980673B2 (en) | 2010-05-08 | 2016-03-02 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US15/095,046 US10188340B2 (en) | 2010-05-08 | 2016-04-09 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US16/210,911 US11253192B2 (en) | 2010-05-08 | 2018-12-05 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US16/440,687 US11779265B2 (en) | 2010-05-08 | 2019-06-13 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US18/346,103 US20230337966A1 (en) | 2010-05-08 | 2023-06-30 | SEM Scanner Sensing Apparatus, System and Methodology for Early Detection of Ulcers |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US16/440,687 Continuation US11779265B2 (en) | 2010-05-08 | 2019-06-13 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
Publications (1)
Publication Number | Publication Date |
---|---|
US20230337966A1 true US20230337966A1 (en) | 2023-10-26 |
Family
ID=44914913
Family Applications (8)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/668,047 Abandoned US20130123587A1 (en) | 2010-05-08 | 2012-11-02 | Sem scanner sensing apparatus, system and methodology for early detection of ulcers |
US14/297,977 Active US9220455B2 (en) | 2010-05-08 | 2014-06-06 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US14/827,375 Active US9398879B2 (en) | 2010-05-08 | 2015-08-17 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US15/058,964 Active US9980673B2 (en) | 2010-05-08 | 2016-03-02 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US15/095,046 Active - Reinstated US10188340B2 (en) | 2010-05-08 | 2016-04-09 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US16/210,911 Active 2032-09-19 US11253192B2 (en) | 2010-05-08 | 2018-12-05 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US16/440,687 Active 2034-06-05 US11779265B2 (en) | 2010-05-08 | 2019-06-13 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US18/346,103 Pending US20230337966A1 (en) | 2010-05-08 | 2023-06-30 | SEM Scanner Sensing Apparatus, System and Methodology for Early Detection of Ulcers |
Family Applications Before (7)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/668,047 Abandoned US20130123587A1 (en) | 2010-05-08 | 2012-11-02 | Sem scanner sensing apparatus, system and methodology for early detection of ulcers |
US14/297,977 Active US9220455B2 (en) | 2010-05-08 | 2014-06-06 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US14/827,375 Active US9398879B2 (en) | 2010-05-08 | 2015-08-17 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US15/058,964 Active US9980673B2 (en) | 2010-05-08 | 2016-03-02 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US15/095,046 Active - Reinstated US10188340B2 (en) | 2010-05-08 | 2016-04-09 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US16/210,911 Active 2032-09-19 US11253192B2 (en) | 2010-05-08 | 2018-12-05 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
US16/440,687 Active 2034-06-05 US11779265B2 (en) | 2010-05-08 | 2019-06-13 | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
Country Status (18)
Country | Link |
---|---|
US (8) | US20130123587A1 (en) |
EP (6) | EP4122383A1 (en) |
JP (4) | JP5763751B2 (en) |
KR (2) | KR101809623B1 (en) |
CN (1) | CN102933958B (en) |
AU (1) | AU2011253253B2 (en) |
BR (3) | BR122021016044B1 (en) |
CA (3) | CA3190351A1 (en) |
DK (1) | DK3581105T3 (en) |
ES (2) | ES2626143T3 (en) |
HK (1) | HK1181847A1 (en) |
HU (1) | HUE059711T2 (en) |
LT (1) | LT3581105T (en) |
PL (1) | PL3581105T3 (en) |
PT (2) | PT2569618T (en) |
SG (1) | SG185131A1 (en) |
SI (1) | SI3581105T1 (en) |
WO (1) | WO2011143071A2 (en) |
Families Citing this family (85)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8389862B2 (en) | 2008-10-07 | 2013-03-05 | Mc10, Inc. | Extremely stretchable electronics |
US9123614B2 (en) | 2008-10-07 | 2015-09-01 | Mc10, Inc. | Methods and applications of non-planar imaging arrays |
US8097926B2 (en) | 2008-10-07 | 2012-01-17 | Mc10, Inc. | Systems, methods, and devices having stretchable integrated circuitry for sensing and delivering therapy |
PL3581105T3 (en) | 2010-05-08 | 2022-11-28 | The Regents Of The University Of California | Apparatus for early detection of ulcers by scanning of subepidermal moisture |
BR112012028410A2 (en) * | 2010-05-08 | 2016-11-16 | Univ California | image registration system and image registration method |
JP5922457B2 (en) * | 2012-03-26 | 2016-05-24 | テルモ株式会社 | Pressure ulcer detection device and its operating method |
US9326685B2 (en) * | 2012-09-14 | 2016-05-03 | Conopco, Inc. | Device for evaluating condition of skin or hair |
US9171794B2 (en) | 2012-10-09 | 2015-10-27 | Mc10, Inc. | Embedding thin chips in polymer |
JP2016500869A (en) | 2012-10-09 | 2016-01-14 | エムシー10 インコーポレイテッドMc10,Inc. | Conformal electronic circuit integrated with clothing |
GB201317746D0 (en) | 2013-10-08 | 2013-11-20 | Smith & Nephew | PH indicator |
CN103271739B (en) * | 2013-05-06 | 2015-04-15 | 清华大学 | Method and device for skin moisture measurement |
US9706647B2 (en) | 2013-05-14 | 2017-07-11 | Mc10, Inc. | Conformal electronics including nested serpentine interconnects |
CN105813545A (en) | 2013-11-22 | 2016-07-27 | Mc10股份有限公司 | Conformal sensor systems for sensing and analysis of cardiac activity |
CA2940539C (en) | 2014-03-04 | 2022-10-04 | Mc10, Inc. | Multi-part flexible encapsulation housing for electronic devices |
WO2015195720A1 (en) * | 2014-06-16 | 2015-12-23 | The Regents Of The University Of California | Methods and apparatus for monitoring wound healing using impedance spectroscopy |
USD781270S1 (en) | 2014-10-15 | 2017-03-14 | Mc10, Inc. | Electronic device having antenna |
WO2016081946A1 (en) * | 2014-11-21 | 2016-05-26 | The Regents Of The University Of California | Fast behavior and abnormality detection |
CN105807981A (en) * | 2014-12-31 | 2016-07-27 | 中兴通讯股份有限公司 | User terminal and working method thereof |
EP3258837A4 (en) | 2015-02-20 | 2018-10-10 | Mc10, Inc. | Automated detection and configuration of wearable devices based on on-body status, location, and/or orientation |
WO2016140961A1 (en) * | 2015-03-02 | 2016-09-09 | Mc10, Inc. | Perspiration sensor |
WO2016172264A1 (en) * | 2015-04-24 | 2016-10-27 | Bruin Biometrics Llc | Apparatus and methods for determining damaged tissue using sub-epidermal moisture measurements |
CA3059988C (en) | 2015-04-24 | 2023-03-07 | Bruin Biometrics, Llc | Apparatus and methods for determining damaged tissue using sub-epidermal moisture measurements |
US20180360344A1 (en) * | 2017-06-19 | 2018-12-20 | Bruin Biometrics, Llc | Apparatus and methods for determining damaged tissue using sub-epidermal moisture measurements |
CN104939796A (en) * | 2015-05-18 | 2015-09-30 | 中国人民解放军第四军医大学 | Visual pocket used for skin grafting |
US10542961B2 (en) | 2015-06-15 | 2020-01-28 | The Research Foundation For The State University Of New York | System and method for infrasonic cardiac monitoring |
RU2018102082A (en) | 2015-07-21 | 2019-08-22 | Конинклейке Филипс Н.В. | DEVICE FOR RADIO-PROCESSING SKIN |
US10709384B2 (en) | 2015-08-19 | 2020-07-14 | Mc10, Inc. | Wearable heat flux devices and methods of use |
EP4079383A3 (en) | 2015-10-01 | 2023-02-22 | Medidata Solutions, Inc. | Method and system for interacting with a virtual environment |
US10532211B2 (en) | 2015-10-05 | 2020-01-14 | Mc10, Inc. | Method and system for neuromodulation and stimulation |
EP3829187A1 (en) | 2016-02-22 | 2021-06-02 | Medidata Solutions, Inc. | System, devices, and method for on-body data and power transmission |
CN108781313B (en) | 2016-02-22 | 2022-04-08 | 美谛达解决方案公司 | System, apparatus and method for a coupled hub and sensor node to obtain sensor information on-body |
US10448881B2 (en) * | 2016-04-15 | 2019-10-22 | Universal Care Solutions, Llc | Systems and methods for classification and treatment of decubitus ulcers |
WO2017184705A1 (en) | 2016-04-19 | 2017-10-26 | Mc10, Inc. | Method and system for measuring perspiration |
WO2017195038A1 (en) | 2016-05-13 | 2017-11-16 | Smith & Nephew Plc | Sensor enabled wound monitoring and therapy apparatus |
WO2017214188A1 (en) | 2016-06-06 | 2017-12-14 | University Of Massachusetts | Systems and methods for prevention of pressure ulcers |
US10447347B2 (en) | 2016-08-12 | 2019-10-15 | Mc10, Inc. | Wireless charger and high speed data off-loader |
GB2600267B (en) | 2017-02-03 | 2022-11-23 | Bruin Biometrics Llc | Measurement of tissue viability |
JP6900477B2 (en) * | 2017-02-03 | 2021-07-07 | ブルーイン、バイオメトリクス、リミテッド、ライアビリティー、カンパニーBruin Biometrics, Llc | A device for assessing compartment syndrome and a computer-readable medium for detecting compartment syndrome |
BR112019008567A2 (en) * | 2017-02-03 | 2019-09-10 | Bruin Biometrics Llc | apparatus for identifying injured tissue and method for identifying damaged tissue |
GB2591708B (en) * | 2017-02-03 | 2021-11-17 | Bruin Biometrics Llc | Measurement of susceptibility to diabetic foot ulcers |
EP3592212A1 (en) | 2017-03-09 | 2020-01-15 | Smith & Nephew PLC | Wound dressing, patch member and method of sensing one or more wound parameters |
US11324424B2 (en) | 2017-03-09 | 2022-05-10 | Smith & Nephew Plc | Apparatus and method for imaging blood in a target region of tissue |
AU2018253383B2 (en) * | 2017-04-11 | 2024-05-09 | Smith & Nephew Plc | Component positioning and stress relief for sensor enabled wound dressings |
JP7272962B2 (en) | 2017-05-15 | 2023-05-12 | スミス アンド ネフュー ピーエルシー | wound analyzer |
AU2018288530B2 (en) | 2017-06-23 | 2024-03-28 | Smith & Nephew Plc | Positioning of sensors for sensor enabled wound monitoring or therapy |
CN109199323B (en) * | 2017-06-29 | 2021-01-26 | 京东方科技集团股份有限公司 | Skin detection device, product information determination method, device and system |
GB201809007D0 (en) | 2018-06-01 | 2018-07-18 | Smith & Nephew | Restriction of sensor-monitored region for sensor-enabled wound dressings |
GB201804502D0 (en) | 2018-03-21 | 2018-05-02 | Smith & Nephew | Biocompatible encapsulation and component stress relief for sensor enabled negative pressure wound therapy dressings |
AU2018312883A1 (en) | 2017-08-10 | 2020-02-20 | Smith & Nephew Plc | Positioning of sensors for sensor enabled wound monitoring or therapy |
GB201718870D0 (en) | 2017-11-15 | 2017-12-27 | Smith & Nephew Inc | Sensor enabled wound therapy dressings and systems |
GB201804971D0 (en) | 2018-03-28 | 2018-05-09 | Smith & Nephew | Electrostatic discharge protection for sensors in wound therapy |
JP2020533093A (en) | 2017-09-10 | 2020-11-19 | スミス アンド ネフュー ピーエルシーSmith & Nephew Public Limited Company | Systems and methods for inspecting encapsulation, as well as components within wound dressings equipped with sensors |
GB201718859D0 (en) | 2017-11-15 | 2017-12-27 | Smith & Nephew | Sensor positioning for sensor enabled wound therapy dressings and systems |
CN111132605B (en) | 2017-09-27 | 2023-05-16 | 史密夫及内修公开有限公司 | PH sensing for negative pressure wound monitoring and treatment device implementing sensor |
WO2019072531A1 (en) | 2017-09-28 | 2019-04-18 | Smith & Nephew Plc | Neurostimulation and monitoring using sensor enabled wound monitoring and therapy apparatus |
JP2021502845A (en) | 2017-11-15 | 2021-02-04 | スミス アンド ネフュー ピーエルシーSmith & Nephew Public Limited Company | Integrated sensor-enabled wound monitoring and / or treatment coverings and systems |
CN116473517A (en) | 2017-11-16 | 2023-07-25 | 布鲁恩生物有限责任公司 | Strategic treatment of pressure ulcers using subsurface moisture values |
WO2019113481A1 (en) * | 2017-12-07 | 2019-06-13 | Bruin Biometrics, Llc | Sem trend analysis |
GB2584226B (en) * | 2018-02-09 | 2022-06-22 | Bruin Biometrics Llc | Detection of tissue damage |
WO2019162272A1 (en) | 2018-02-21 | 2019-08-29 | T.J.Smith And Nephew, Limited | Monitoring of body loading and body position for the treatment of pressure ulcers or other injuries |
US11451965B2 (en) | 2018-06-04 | 2022-09-20 | T.J.Smith And Nephew, Limited | Device communication management in user activity monitoring systems |
EP3586724A1 (en) * | 2018-06-27 | 2020-01-01 | Koninklijke Philips N.V. | Device for use in determining a hydration level of skin |
CN113164076A (en) * | 2018-07-24 | 2021-07-23 | 巴克斯特国际公司 | Patch-based physiological sensor |
US11096590B2 (en) * | 2018-07-24 | 2021-08-24 | Baxter International Inc. | Patch-based physiological sensor |
US10842392B2 (en) * | 2018-07-24 | 2020-11-24 | Baxter International Inc. | Patch-based physiological sensor |
US11202578B2 (en) * | 2018-07-24 | 2021-12-21 | Welch Allyn, Inc. | Patch-based physiological sensor |
US11116410B2 (en) | 2018-07-24 | 2021-09-14 | Baxter International Inc. | Patch-based physiological sensor |
US11064918B2 (en) | 2018-07-24 | 2021-07-20 | Baxter International Inc. | Patch-based physiological sensor |
US11404296B2 (en) | 2018-09-04 | 2022-08-02 | Applied Materials, Inc. | Method and apparatus for measuring placement of a substrate on a heater pedestal |
US10847393B2 (en) | 2018-09-04 | 2020-11-24 | Applied Materials, Inc. | Method and apparatus for measuring process kit centering |
US11342210B2 (en) | 2018-09-04 | 2022-05-24 | Applied Materials, Inc. | Method and apparatus for measuring wafer movement and placement using vibration data |
US10794681B2 (en) * | 2018-09-04 | 2020-10-06 | Applied Materials, Inc. | Long range capacitive gap measurement in a wafer form sensor system |
US11521872B2 (en) | 2018-09-04 | 2022-12-06 | Applied Materials, Inc. | Method and apparatus for measuring erosion and calibrating position for a moving process kit |
GB2592508B (en) | 2018-09-12 | 2022-08-31 | Smith & Nephew | Device, apparatus and method of determining skin perfusion pressure |
GB2591711B (en) | 2018-10-11 | 2022-02-02 | Bruin Biometrics Llc | Device with detachable element |
GB2577927B (en) * | 2018-10-11 | 2023-07-26 | Zedsen Ltd | An Apparatus for Producing Output Data Relating to Skin Conditions |
CN109596264A (en) * | 2018-11-14 | 2019-04-09 | 珠海市万瑙特健康科技有限公司 | Array pressure sensor detecting device |
CN111195180A (en) * | 2018-11-16 | 2020-05-26 | 希尔-罗姆服务公司 | System and method for determining a target pressure injury score and modifying a treatment plan based thereon |
GB201820927D0 (en) | 2018-12-21 | 2019-02-06 | Smith & Nephew | Wound therapy systems and methods with supercapacitors |
US20210076974A1 (en) * | 2019-09-17 | 2021-03-18 | Bruin Biometrics, Llc | System for Strategic Monitoring and Treatment of Pressure Ulcer Using Sub-Epidermal Moisture Values |
JP2023520879A (en) * | 2020-04-03 | 2023-05-22 | ブルーイン、バイオメトリクス、リミテッド、ライアビリティー、カンパニー | biocapacitance sensor |
CN112315428B (en) * | 2020-11-03 | 2021-12-28 | 兰州大学 | Optical sensing device for measuring human body pressure injury |
WO2022169850A1 (en) | 2021-02-03 | 2022-08-11 | Bruin Biometrics, Llc | Methods of treating deep and early-stage pressure induced tissue damage |
WO2023183440A1 (en) * | 2022-03-23 | 2023-09-28 | Nikon Corporation | Flexible skin sensors for skin hydration measurements |
CN117281478B (en) * | 2023-10-17 | 2024-05-28 | 天津大学 | Skin disease auxiliary diagnosis device and system |
Citations (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5152296A (en) * | 1990-03-01 | 1992-10-06 | Hewlett-Packard Company | Dual-finger vital signs monitor |
US20020032485A1 (en) * | 2000-03-29 | 2002-03-14 | Eric Flam | Apparatus and methods for preventing and/or healing pressure ulcers |
US20060239547A1 (en) * | 2005-04-20 | 2006-10-26 | Robinson M R | Use of optical skin measurements to determine cosmetic skin properties |
US20070051362A1 (en) * | 2004-04-23 | 2007-03-08 | Sullivan Timothy R | Multiple unit dose drug delivery system |
US20070185392A1 (en) * | 2005-09-02 | 2007-08-09 | Sherman Faiz F | Method and device for indicating moisture content of skin |
US20080054276A1 (en) * | 2006-08-31 | 2008-03-06 | Fraunhofer-Gesellschaft Zur Forderung Der Angerwandten Forschung E.V. | Reflex coupler with integrated organic light emitter |
US20080063363A1 (en) * | 2006-08-31 | 2008-03-13 | Georgia Tech Research | Method and computer program product for synchronizing, displaying, and providing access to data collected from various media |
US20080166268A1 (en) * | 2007-01-10 | 2008-07-10 | Hiroshi Yamaguchi | Test sheet, apparatus, method and program for diagnosing an object |
US20090054752A1 (en) * | 2007-08-22 | 2009-02-26 | Motorola, Inc. | Method and apparatus for photoplethysmographic sensing |
US20090306487A1 (en) * | 2006-04-11 | 2009-12-10 | The University Of Nottingham | Photoplethysmography |
Family Cites Families (259)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3851641A (en) | 1973-11-29 | 1974-12-03 | J Toole | Method and apparatus for determining internal impedance of animal body part |
US4295009A (en) | 1980-03-07 | 1981-10-13 | Amp Incorporated | Piezoelectric audio transducer mounting and electrical connector |
US4557271A (en) | 1983-05-11 | 1985-12-10 | Stoller Kenneth P | Method and apparatus for detecting body illness, dysfunction, disease and/or pathology |
US4857716A (en) | 1986-05-12 | 1989-08-15 | Clinicom Incorporated | Patient identification and verification system and method |
JPH0524131Y2 (en) | 1986-11-07 | 1993-06-18 | ||
US4860753A (en) | 1987-11-04 | 1989-08-29 | The Gillette Company | Monitoring apparatus |
FR2629204B1 (en) * | 1988-03-25 | 1990-12-14 | Oreal | DEVICE FOR PERFORMING A MEASUREMENT OF THE WATER CONTENT OF A SUBSTRATE, IN PARTICULAR OF THE SKIN |
US5158091A (en) * | 1990-11-30 | 1992-10-27 | Ivac Corporation | Tonometry system for determining blood pressure |
US5226245A (en) | 1991-09-20 | 1993-07-13 | Lamont William D | Protective boot structure |
WO1993012708A2 (en) | 1991-12-17 | 1993-07-08 | Kinetic Concepts, Inc. | Pneumatic compression device for medical use |
US5292341A (en) | 1992-03-02 | 1994-03-08 | Siemens Pacesetter, Inc. | Method and system for determining and automatically adjusting the sensor parameters of a rate-responsive pacemaker |
US5664231A (en) | 1994-04-29 | 1997-09-02 | Tps Electronics | PCMCIA interface card for coupling input devices such as barcode scanning engines to personal digital assistants and palmtop computers |
NO180024C (en) | 1994-10-11 | 1997-01-29 | Oerjan G Martinsen | Measurement of moisture in the skin |
US6671563B1 (en) | 1995-05-15 | 2003-12-30 | Alaris Medical Systems, Inc. | System and method for collecting data and managing patient care |
US20010051783A1 (en) * | 1996-02-23 | 2001-12-13 | Stuart D. Edwards | Method and apparatus for treatment of air way obstructions |
US5815416A (en) | 1996-04-19 | 1998-09-29 | Vlsi Technology, Inc. | Method of measuring energy consumption in a circuit simulator |
US6135781A (en) | 1996-07-17 | 2000-10-24 | Minnesota Mining And Manufacturing Company | Electrical interconnection system and device |
US6778090B2 (en) * | 1996-09-04 | 2004-08-17 | Paul Newham | Modular system for monitoring the presence of a person using a variety of sensing devices |
US7657297B2 (en) * | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
US20050096513A1 (en) * | 1997-11-11 | 2005-05-05 | Irvine Sensors Corporation | Wearable biomonitor with flexible thinned integrated circuit |
US6949816B2 (en) * | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
US6175752B1 (en) * | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6223088B1 (en) | 1998-11-09 | 2001-04-24 | Katecho, Incorporated | Electrode and connector assembly and method for using same |
US6330479B1 (en) * | 1998-12-07 | 2001-12-11 | The Regents Of The University Of California | Microwave garment for heating and/or monitoring tissue |
EP1171030B1 (en) | 1999-04-20 | 2006-11-02 | Nova Technology Corporation | Method and apparatus for measuring relative hydration of a substrate |
JP2001110488A (en) | 1999-08-04 | 2001-04-20 | Japan Aviation Electronics Industry Ltd | Connector structure for connecting substrates |
JP3722654B2 (en) | 1999-09-03 | 2005-11-30 | 株式会社タニタ | Physical condition recovery judgment device after childbirth |
US6368284B1 (en) | 1999-11-16 | 2002-04-09 | Cardiac Intelligence Corporation | Automated collection and analysis patient care system and method for diagnosing and monitoring myocardial ischemia and outcomes thereof |
JP2001178705A (en) | 1999-12-22 | 2001-07-03 | Sousei Denshi:Kk | Contact type measuring device |
AU2001229916A1 (en) | 2000-01-27 | 2001-08-07 | National Research Council Of Canada | Visible-near infrared spectroscopy in burn injury assessment |
US20020016535A1 (en) | 2000-01-28 | 2002-02-07 | Martin W. Blake | Subcutaneous glucose measurement device |
US6738798B1 (en) | 2000-06-01 | 2004-05-18 | Ge Medical Technology Services, Inc. | Automated monitoring of collection of operational data from medical imaging devices |
US7030764B2 (en) | 2000-06-09 | 2006-04-18 | Bed-Check Corporation | Apparatus and method for reducing the risk of decubitus ulcers |
DE60114318T2 (en) * | 2000-07-03 | 2006-07-13 | Matsushita Electric Works, Ltd., Kadoma | Capacitive moisture sensor and method for its manufacture |
JP3866943B2 (en) | 2000-08-04 | 2007-01-10 | 株式会社タニタ | Weight management device |
US6606510B2 (en) | 2000-08-31 | 2003-08-12 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding patient data |
KR100864415B1 (en) | 2000-12-14 | 2008-10-20 | 가부시키가이샤 피지온 | Body impedance measuring instrument |
US7315767B2 (en) * | 2001-03-06 | 2008-01-01 | Solianis Holding Ag | Impedance spectroscopy based systems and methods |
FI109651B (en) | 2001-03-23 | 2002-09-30 | Delfin Technologies Ltd | Procedure for measuring edema in tissues |
WO2002076289A2 (en) | 2001-03-27 | 2002-10-03 | Kain Aron Z | Wireless system for measuring distension in flexible tubes |
US6577700B1 (en) | 2001-06-22 | 2003-06-10 | Liang-Shih Fan | Neural network based multi-criteria optimization image reconstruction technique for imaging two- and three-phase flow systems using electrical capacitance tomography |
DE60215668T2 (en) * | 2001-07-26 | 2007-08-30 | Medrad, Inc. | ELECTROMAGNETIC SENSORS FOR BIOLOGICAL TISSUE APPLICATIONS |
WO2003009753A2 (en) * | 2001-07-26 | 2003-02-06 | Chad Bouton | Detection of fluids in tissue |
US20030116447A1 (en) * | 2001-11-16 | 2003-06-26 | Surridge Nigel A. | Electrodes, methods, apparatuses comprising micro-electrode arrays |
JP2003169788A (en) | 2001-12-05 | 2003-06-17 | Matsushita Electric Ind Co Ltd | Skin water content measuring instrument |
JP2003169787A (en) * | 2001-12-05 | 2003-06-17 | Matsushita Electric Ind Co Ltd | Skin water content measuring instrument |
US20030110662A1 (en) | 2001-12-13 | 2003-06-19 | Gilman Thomas H. | Adherent orthotic pad |
WO2003076009A1 (en) | 2002-03-06 | 2003-09-18 | Loma Linda University | Method and device for wound healing |
JP4071979B2 (en) | 2002-03-29 | 2008-04-02 | 株式会社フィジオン | Standing body composition measuring device |
US6634045B1 (en) | 2002-04-01 | 2003-10-21 | Dudonis Matt | Heel elevator support |
US6963772B2 (en) | 2002-04-17 | 2005-11-08 | The Board Of Trustees Of The Leland Stanford Junior University | User-retainable temperature and impedance monitoring methods and devices |
JP3704685B2 (en) * | 2002-07-29 | 2005-10-12 | 株式会社山武 | Capacitance sensor |
US8111165B2 (en) * | 2002-10-02 | 2012-02-07 | Orthocare Innovations Llc | Active on-patient sensor, method and system |
GB0228375D0 (en) | 2002-12-05 | 2003-01-08 | Innovation And Entpr Off Of | Wound mapping |
FR2849764B1 (en) * | 2003-01-14 | 2012-12-14 | Oreal | DEVICE AND METHOD, IN PARTICULAR FOR EVALUATING THE MOISTURIZATION OF THE SKIN OR MUCOSES |
WO2004080279A2 (en) | 2003-03-06 | 2004-09-23 | Spectragenics, Inc. | In the patent cooperation treaty application for patent |
FI20030806A0 (en) | 2003-05-28 | 2003-05-28 | Delfin Technologies Ltd | A method for measuring the amount of water in existing fat tissues and apparatus for applying the method |
US7725151B2 (en) | 2003-06-02 | 2010-05-25 | Van Der Weide Daniel Warren | Apparatus and method for near-field imaging of tissue |
US20050027175A1 (en) | 2003-07-31 | 2005-02-03 | Zhongping Yang | Implantable biosensor |
JP2005052227A (en) * | 2003-08-07 | 2005-03-03 | Naoyuki Minorikawa | Instrument measuring water content of stratum corneum non-affected by electrolyte component on skin surface |
EP2382920A1 (en) | 2003-08-20 | 2011-11-02 | Philometron, Inc. | Hydration monitoring |
US20050251418A1 (en) | 2003-10-15 | 2005-11-10 | Cerner Innovation, Inc. | System and method for processing ad hoc orders in an automated patient care environment |
US20050086072A1 (en) | 2003-10-15 | 2005-04-21 | Fox Charles S.Jr. | Task-based system and method for managing patient care through automated recognition |
JP2005253840A (en) | 2004-03-15 | 2005-09-22 | Tanita Corp | Skin condition estimating device |
TW200534827A (en) | 2004-03-24 | 2005-11-01 | Noninvasive Medical Technologies Llc | Thoracic impedance monitor and electrode array and method of use |
JP4157873B2 (en) * | 2004-04-01 | 2008-10-01 | 株式会社日本システム研究所 | Surface texture measuring probe, and surface texture measuring method and apparatus using the probe |
US8060315B2 (en) | 2004-07-27 | 2011-11-15 | Carefusion 303, Inc. | Method for measuring the incidence of hospital acquired infections |
US20060052678A1 (en) | 2004-09-02 | 2006-03-09 | Drinan Darrel D | Monitoring platform for wound and ulcer monitoring and detection |
EP1803464A4 (en) | 2004-09-17 | 2009-09-09 | Cellgentech Inc | External preparation for treating skin ulcer |
US7358927B2 (en) | 2004-10-26 | 2008-04-15 | Eaton Corporation | Antenna employing a cover |
WO2006048789A1 (en) * | 2004-11-05 | 2006-05-11 | Koninklijke Philips Electronics N. V. | Detection apparatus and method for use with biosensor emitting rf signals |
US8092380B2 (en) | 2005-02-28 | 2012-01-10 | Rothman Healthcare Corporation | System and method for improving hospital patient care by providing a continual measurement of health |
US20080009764A1 (en) | 2005-04-21 | 2008-01-10 | Epi-Sci, Llc | Method and system for detecting electrophysiological changes in pre-cancerous and cancerous tissue and epithelium |
US8287451B2 (en) * | 2005-05-19 | 2012-10-16 | Industrial Technology Research Institute | Flexible biomonitor with EMI shielding and module expansion |
US7301350B2 (en) | 2005-06-03 | 2007-11-27 | Synaptics Incorporated | Methods and systems for detecting a capacitance using sigma-delta measurement techniques |
WO2007000164A2 (en) * | 2005-06-27 | 2007-01-04 | Sense A/S | Apparatus for determination of blood pressure |
JP4418419B2 (en) * | 2005-09-30 | 2010-02-17 | 有限会社アミカ | Skin condition evaluation apparatus, skin condition evaluation program, and computer-readable storage medium storing the program |
US7733224B2 (en) | 2006-06-30 | 2010-06-08 | Bao Tran | Mesh network personal emergency response appliance |
JP5588108B2 (en) | 2005-10-24 | 2014-09-10 | アブリュー マルシオ マルク | Biological parameter measuring apparatus and method |
EP2329764A3 (en) * | 2005-11-10 | 2011-10-19 | Solianis Holding AG | Device for determining the glucose level in body tissue |
US7691101B2 (en) | 2006-01-06 | 2010-04-06 | Arthrocare Corporation | Electrosurgical method and system for treating foot ulcer |
US20070179585A1 (en) | 2006-01-31 | 2007-08-02 | Mark Chandler | Method and apparatus for treating a wound |
US9198981B2 (en) | 2006-02-01 | 2015-12-01 | The University Of Kentucky | Modulation of angiogenesis |
US8473262B2 (en) | 2008-08-14 | 2013-06-25 | ARETé ASSOCIATES | Self-cleaning submerged instrumentation |
BRPI0707961A2 (en) | 2006-02-28 | 2011-05-10 | Coloplast As | Method for detecting detachment of a dressing, appropriate dressing for applying the method, sensor assembly, and shield to reduce capacitive coupling from the environmental vicinity to the dressing electrodes |
US20070248542A1 (en) | 2006-04-24 | 2007-10-25 | Bodybio, Inc. | Devices and methods for individualized detection of nutrient imbalance via olfactory system |
GB2439750A (en) | 2006-07-06 | 2008-01-09 | Wound Solutions Ltd | Monitoring a limb wound |
US20080015894A1 (en) | 2006-07-17 | 2008-01-17 | Walgreen Co. | Health Risk Assessment Of A Medication Therapy Regimen |
US8116852B2 (en) | 2006-09-29 | 2012-02-14 | Nellcor Puritan Bennett Llc | System and method for detection of skin wounds and compartment syndromes |
US20090047694A1 (en) | 2007-08-17 | 2009-02-19 | Shuber Anthony P | Clinical Intervention Directed Diagnostic Methods |
US8845554B2 (en) * | 2007-03-09 | 2014-09-30 | The Regents Of The University Of California | Method and apparatus for quantitative assessment of neuromotor disorders |
US7374460B1 (en) | 2007-04-17 | 2008-05-20 | Traxxas Lp | Electrical connector assembly |
CN101707872B (en) | 2007-04-27 | 2014-10-22 | 回声治疗有限公司 | skin permeation device for analyte sensing or transdermal drug delivery |
EP2006786B1 (en) | 2007-06-18 | 2018-05-09 | Roche Diabetes Care GmbH | Method and glucose monitoring system for monitoring individual metabolic response and for generating nutritional feedback |
US20090009193A1 (en) * | 2007-07-06 | 2009-01-08 | Chung Yuan Christian University | Moisture-Sensitive Element with an Interdigital Capacitor and Fabrication thereof |
US20110046505A1 (en) | 2007-08-09 | 2011-02-24 | Impedimed Limited | Impedance measurement process |
WO2009036369A1 (en) | 2007-09-14 | 2009-03-19 | Corventis, Inc. | System and methods for wireless body fluid monitoring |
US20090076345A1 (en) * | 2007-09-14 | 2009-03-19 | Corventis, Inc. | Adherent Device with Multiple Physiological Sensors |
WO2009038964A1 (en) | 2007-09-19 | 2009-03-26 | Persimmon Scientific | Devices for prevention of pressure ulcers |
CN101420076A (en) | 2007-10-22 | 2009-04-29 | 鸿富锦精密工业(深圳)有限公司 | Connector component |
US7603171B2 (en) | 2007-10-25 | 2009-10-13 | Fresh Medical Laboratories, Inc. | Method for diagnosing a disease |
JP4444338B2 (en) | 2008-01-30 | 2010-03-31 | 三菱重工業株式会社 | Radiotherapy apparatus control apparatus and radiation irradiation method |
JP5317527B2 (en) | 2008-05-02 | 2013-10-16 | 花王株式会社 | Method for estimating the internal structure of the skin at a spot |
WO2009144615A1 (en) | 2008-05-26 | 2009-12-03 | Koninklijke Philips Electronics N.V. | Moisture control within a multi-electrode patch for monitoring and electrical stimulation of wound healing |
US9326711B2 (en) | 2008-06-30 | 2016-05-03 | Medtronic, Inc. | Optical perfusion sensor detector |
WO2010009269A2 (en) | 2008-07-15 | 2010-01-21 | Piedmont Healthcare, Inc. | Method for coronary artery disease risk assessment |
US20110191122A1 (en) | 2008-09-15 | 2011-08-04 | ZocDoc, Inc. | Method and apparatus for managing physician referrals |
EP2337492A1 (en) | 2008-09-22 | 2011-06-29 | Cardiac Pacemakers, Inc. | Congestive heart failure decompensation detection |
AU2009308500A1 (en) | 2008-10-21 | 2010-04-29 | PeraHealth, Inc | Methods of assessing risk based on medical data and uses thereof |
US8574851B2 (en) | 2008-11-24 | 2013-11-05 | Corthera, Inc. | Prediction and prevention of preeclampsia |
WO2010060152A1 (en) | 2008-11-28 | 2010-06-03 | Impedimed Limited | Impedance measurement process |
WO2010068797A1 (en) | 2008-12-10 | 2010-06-17 | Waverx, Inc. | Devices, systems and methods for preventing and treating sensation loss |
DE102009008885A1 (en) | 2009-02-14 | 2010-08-26 | Fresenius Medical Care Deutschland Gmbh | Device for detecting moisture for a device for monitoring access to a patient, in particular for monitoring the vascular access in the case of extracorporeal blood treatment |
US8246615B2 (en) | 2009-05-19 | 2012-08-21 | Vivant Medical, Inc. | Tissue impedance measurement using a secondary frequency |
KR101006824B1 (en) | 2009-05-22 | 2011-01-10 | 한국과학기술원 | Wearable monitoring apparatus and driving method thereof |
US20100324455A1 (en) | 2009-05-23 | 2010-12-23 | Lasercure Sciences, Inc. | Devices for management of foot injuries and methods of use and manufacture thereof |
US9345531B2 (en) | 2009-06-05 | 2016-05-24 | Cynosure, Inc. | Radio-frequency treatment of skin tissue with shock-free handpiece |
GB0912009D0 (en) | 2009-07-10 | 2009-08-19 | Univ Strathclyde | Sensor |
EP2467058A4 (en) | 2009-08-17 | 2014-08-06 | Univ California | Distributed external and internal wireless sensor systems for characterization of surface and subsurface biomedical structure and condition |
US8390583B2 (en) * | 2009-08-31 | 2013-03-05 | Qualcomm Incorporated | Pressure sensitive user interface for mobile devices |
US9579039B2 (en) | 2011-01-10 | 2017-02-28 | Masimo Corporation | Non-invasive intravascular volume index monitor |
EP2302606B1 (en) | 2009-09-23 | 2013-06-05 | Dräger Medical GmbH | Method for alarm generation, control device and device for carrying out the method |
PL2308372T3 (en) | 2009-10-01 | 2017-07-31 | Seca Ag | Bioimpedance measuring device |
EP2493374B1 (en) | 2009-10-28 | 2016-12-14 | The Board of Governors for Higher Education, State of Rhode Island and Providence Plantations | Biomedical electrode |
US20120308623A1 (en) | 2009-12-15 | 2012-12-06 | Sebastien Francis Michel Taxt-Lamolle | Composition comprising nanoparticles of ti02 |
US10441185B2 (en) * | 2009-12-16 | 2019-10-15 | The Board Of Trustees Of The University Of Illinois | Flexible and stretchable electronic systems for epidermal electronics |
NO20093601A1 (en) | 2009-12-29 | 2011-06-30 | Idex Asa | surface Sensor |
US8874186B2 (en) | 2009-12-30 | 2014-10-28 | Avery Dennison Corporation | Apparatus and method for monitoring physiological parameters using electrical measurements |
US8519974B2 (en) * | 2010-01-19 | 2013-08-27 | Sony Corporation | Touch sensing device, touch screen device comprising the touch sensing device, mobile device, method for sensing a touch and method for manufacturing a touch sensing device |
CA2786917A1 (en) | 2010-01-27 | 2011-08-04 | Robert Miller | Risk modeling for pressure ulcer formation |
US8828330B2 (en) | 2010-01-28 | 2014-09-09 | Abbott Diabetes Care Inc. | Universal test strip port |
WO2011106792A2 (en) * | 2010-02-26 | 2011-09-01 | Myskin, Inc. | Analytic methods of tissue evaluation |
JP6192032B2 (en) | 2010-04-22 | 2017-09-06 | リーフ ヘルスケア インコーポレイテッド | A system for monitoring a patient's physiological status |
BR112012028410A2 (en) | 2010-05-08 | 2016-11-16 | Univ California | image registration system and image registration method |
PL3581105T3 (en) | 2010-05-08 | 2022-11-28 | The Regents Of The University Of California | Apparatus for early detection of ulcers by scanning of subepidermal moisture |
WO2012037272A2 (en) | 2010-09-14 | 2012-03-22 | University Of Southern California | Concentric bipolar electrochemical impedance spectroscopy to assess vascular oxidative stress |
US20120078088A1 (en) | 2010-09-28 | 2012-03-29 | Point of Contact, LLC. | Medical image projection and tracking system |
NZ611197A (en) | 2010-10-29 | 2015-07-31 | Orpyx Medical Technologies Inc | Peripheral sensory and supersensory replacement system |
US20120271121A1 (en) | 2010-12-29 | 2012-10-25 | Basis Science, Inc. | Integrated Biometric Sensing and Display Device |
TWI560200B (en) | 2011-05-25 | 2016-12-01 | Innate Pharma Sa | Anti-kir antibodies for the treatment of inflammatory and autoimmune disorders |
DE102012011212B4 (en) | 2011-06-06 | 2016-02-11 | Technische Universität Dresden | Sensor for determining the degree of infection of a wound under dressings |
CN105963074B (en) | 2011-07-14 | 2020-01-17 | 史密夫及内修公开有限公司 | Wound dressing and method of treatment |
DE102011113839B4 (en) | 2011-09-21 | 2013-05-02 | Fresenius Medical Care Deutschland Gmbh | Connection terminal for a humidity sensor and arrangement of a humidity sensor and a connection terminal for monitoring a vascular access and device for monitoring a vascular access |
CN104219999A (en) | 2012-01-30 | 2014-12-17 | 感官系统公司 | Sensors, interfaces and sensor systems for data collection and integrated remote monitoring of conditions at or near body surfaces |
JP5922457B2 (en) | 2012-03-26 | 2016-05-24 | テルモ株式会社 | Pressure ulcer detection device and its operating method |
CN105283122B (en) | 2012-03-30 | 2020-02-18 | 伊利诺伊大学评议会 | Appendage mountable electronic device conformable to a surface |
DK2833783T4 (en) | 2012-04-02 | 2020-10-19 | Podimetrics Inc | METHOD AND DEVICE FOR INDICATING THE OCCURRENCE OF BEGINNING, OPEN WOUNDS AND ITS PROGRESSION |
US10265219B2 (en) | 2012-04-12 | 2019-04-23 | Elwha Llc | Wound dressing monitoring systems including appurtenances for wound dressings |
KR101347256B1 (en) | 2012-05-08 | 2014-01-06 | 루미리치 주식회사 | LED lighting apparatus |
UY34812A (en) | 2012-05-18 | 2013-12-31 | Teva Pharma | METHOD FOR TREATMENT OF LUNG CANCER OF NON-SMALL CELLS |
US20150186607A1 (en) | 2012-08-24 | 2015-07-02 | Koninklijke Philips N.V. | Clinical support system and method |
US9979206B2 (en) | 2012-09-07 | 2018-05-22 | Solace Power Inc. | Wireless electric field power transfer system, method, transmitter and receiver therefor |
US8945328B2 (en) | 2012-09-11 | 2015-02-03 | L.I.F.E. Corporation S.A. | Methods of making garments having stretchable and conductive ink |
US9901298B2 (en) | 2012-11-01 | 2018-02-27 | Quaerimus Medical Incorporated | System and method for prevention of diabetic foot ulcers using total internal reflection imaging |
US20140142984A1 (en) | 2012-11-21 | 2014-05-22 | Datcard Systems, Inc. | Cloud based viewing, transfer and storage of medical data |
TWI651106B (en) | 2012-12-24 | 2019-02-21 | 伯林格公司 | Catheter or cannula arrangement and method for monitoring length of stay of the same in a body |
US20140200486A1 (en) | 2013-01-17 | 2014-07-17 | Quaerimus, Inc. | System and method for continuous monitoring of a human foot for signs of ulcer development |
US20150371522A1 (en) | 2013-01-28 | 2015-12-24 | Sensimat Systems Inc. | Multi-Station System for Pressure Ulcer Monitoring and Analysis |
US10463273B2 (en) | 2013-02-01 | 2019-11-05 | Halo Wearables, Llc | Hydration monitor |
US20140316297A1 (en) | 2013-02-22 | 2014-10-23 | Noninvasive Medical Technologies, Inc. | Impedance monitors, electrode arrays and methods of use |
US20140273025A1 (en) | 2013-03-15 | 2014-09-18 | Wallac Oy | System and method for determining risk of pre-eclampsia based on biochemical marker analysis |
US9808170B2 (en) | 2013-03-15 | 2017-11-07 | Welch Allyn, Inc. | Electrode with charge-operated indicator |
BR112015028905A2 (en) | 2013-05-21 | 2017-07-25 | Orpyx Medical Tech Inc | pressure data acquisition set and method of acquiring pressure data |
WO2014188070A1 (en) | 2013-05-23 | 2014-11-27 | Åbo Akademi University | An arrangement for facilitating wound healing, a method for measuring wound healing and a wound dressing |
US10206604B2 (en) | 2013-05-23 | 2019-02-19 | Cutosense Oy | Arrangement for facilitating wound healing, a method for measuring wound healing and a wound dressing |
US20150002168A1 (en) | 2013-06-27 | 2015-01-01 | General Electric Company | Systems and methods for soft-field tomography |
WO2015003015A2 (en) | 2013-07-01 | 2015-01-08 | Intersection Medical, Inc. | Compact and wearable apparatuses for home use in determining tissue wetness |
US9729730B2 (en) | 2013-07-02 | 2017-08-08 | Immersion Corporation | Systems and methods for perceptual normalization of haptic effects |
US9999352B2 (en) | 2013-09-27 | 2018-06-19 | General Electric Company | System and method for determining a hydration level of a tissue region |
CN103815875B (en) | 2013-10-28 | 2015-06-03 | 重庆西南医院 | Near-infrared spectrum imaging system for diagnosis of depth and area of burn skin necrosis |
WO2015077838A1 (en) | 2013-11-28 | 2015-06-04 | University Of Western Sydney | "blood volume monitor" |
US20150157435A1 (en) | 2013-12-06 | 2015-06-11 | PegaSense, Inc. | Equine fitness monitor |
US9028407B1 (en) | 2013-12-13 | 2015-05-12 | Safer Care LLC | Methods and apparatus for monitoring patient conditions |
EP3108392A1 (en) | 2014-02-18 | 2016-12-28 | Tria Beauty, Inc. | Internet connected dermatological devices and systems |
US10898133B1 (en) | 2014-02-18 | 2021-01-26 | Orbital Reserach Inc. | Head-mounted physiological signal monitoring system, devices and methods |
WO2015168720A1 (en) | 2014-05-07 | 2015-11-12 | University Of South Australia | Wound sensor, system and method |
JP2017514620A (en) | 2014-05-07 | 2017-06-08 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Method and apparatus for estimating fluid content of a body part of a subject |
US20150363567A1 (en) | 2014-06-13 | 2015-12-17 | T.K. Pettus LLC | Comprehensive health assessment system and method |
WO2015195720A1 (en) | 2014-06-16 | 2015-12-23 | The Regents Of The University Of California | Methods and apparatus for monitoring wound healing using impedance spectroscopy |
WO2015196298A1 (en) * | 2014-06-26 | 2015-12-30 | Biopeak Corporation | A multi-parameter sensor system for measuring physiological signals |
US20160015962A1 (en) | 2014-07-16 | 2016-01-21 | Mehdi Shokoueinejad Maragheh | Smart Patch For Wound Management |
BR112017001135A2 (en) | 2014-07-24 | 2018-01-30 | Koninklijke Philips Nv | noninvasive treatment device for heating a first internal region and a second internal region of the skin using radiofrequency (rf) electric current |
US9770185B2 (en) | 2014-08-06 | 2017-09-26 | Verily Life Sciences Llc | Sharing a single electrode between skin resistance and capacitance measurements |
US10321858B2 (en) | 2014-08-18 | 2019-06-18 | Proteadx, Inc. | Apparatus and methods for transdermal sensing of analytes in interstitial fluid and associated data transmission systems |
CN204119175U (en) | 2014-09-23 | 2015-01-21 | 成都玖信科技有限公司 | A kind of ultra-wideband microwave power amplifier module based on PCB technology |
US10117617B2 (en) | 2014-10-08 | 2018-11-06 | Revealix, Inc. | Automated systems and methods for skin assessment and early detection of a latent pathogenic bio-signal anomaly |
US9717417B2 (en) | 2014-10-29 | 2017-08-01 | Spectral Md, Inc. | Reflective mode multi-spectral time-resolved optical imaging methods and apparatuses for tissue classification |
CN104352230A (en) | 2014-11-10 | 2015-02-18 | 电子科技大学 | Non-invasive thrombosis detector |
US10285898B2 (en) | 2014-12-10 | 2019-05-14 | Nextern Inc. | Responsive whole patient care compression therapy and treatment system |
US10201198B2 (en) | 2014-12-23 | 2019-02-12 | Profit Royal Pharmaceutical Limited | Protective masks with coating comprising different electrospun fibers interweaved with each other, formulations forming the same, and method of producing thereof |
CN104567657A (en) | 2014-12-23 | 2015-04-29 | 天津大学 | Method for representing metal surface corrosion roughness based on electrochemical impedance spectra |
FR3032184B1 (en) | 2015-02-03 | 2017-02-10 | Qualipac Sa | COMMUNICATION SYSTEM AND METHOD USING A CONTAINER FOR A COSMETIC OR PHARMACEUTICAL PRODUCT OR A WINE OR A SPIRITUAL AND TWO MOBILE TELECOMMUNICATION EQUIPMENT |
US20160270968A1 (en) | 2015-03-20 | 2016-09-22 | Amanda J. Stanford | Two-part bandage with replaceable wound covering portion |
US10058256B2 (en) | 2015-03-20 | 2018-08-28 | East Carolina University | Multi-spectral laser imaging (MSLI) methods and systems for blood flow and perfusion imaging and quantification |
CA2981474A1 (en) | 2015-03-31 | 2016-10-06 | Oncosec Medical Incorporated | Systems and methods for improved tissue-sensing based electroporation |
US10314638B2 (en) | 2015-04-07 | 2019-06-11 | Ethicon Llc | Articulating radio frequency (RF) tissue seal with articulating state sensing |
RU2017134674A (en) | 2015-04-08 | 2019-04-05 | Конинклейке Филипс Н.В. | NON-INVASIVE DEVICE FOR SKIN TREATMENT USING A RADIO-FREQUENCY (RF) ELECTRIC CURRENT, WITH A TREATMENT SETTING DETECTION UNIT |
US20180360344A1 (en) | 2017-06-19 | 2018-12-20 | Bruin Biometrics, Llc | Apparatus and methods for determining damaged tissue using sub-epidermal moisture measurements |
WO2016172264A1 (en) | 2015-04-24 | 2016-10-27 | Bruin Biometrics Llc | Apparatus and methods for determining damaged tissue using sub-epidermal moisture measurements |
CA3059988C (en) | 2015-04-24 | 2023-03-07 | Bruin Biometrics, Llc | Apparatus and methods for determining damaged tissue using sub-epidermal moisture measurements |
US20160338591A1 (en) | 2015-05-21 | 2016-11-24 | Hill-Rom Services, Inc. | Systems and methods for mitigating tissue breakdown |
US10149958B1 (en) | 2015-07-17 | 2018-12-11 | Bao Tran | Systems and methods for computer assisted operation |
WO2017032393A1 (en) | 2015-08-21 | 2017-03-02 | Qimova A/S | System and process for controlling the risks of appearance of pressure ulcers |
US10448844B2 (en) | 2015-08-31 | 2019-10-22 | Masimo Corporation | Systems and methods for patient fall detection |
CA2997650A1 (en) | 2015-09-05 | 2017-03-09 | Nova Southeastern University | Detecting early tissue damage due to mechanical deformation, shear, friction, and/or prolonged application of pressure |
CN108697341B (en) | 2015-12-16 | 2022-03-04 | 塞仁护理公司 | System and method for detecting foot inflammation |
US10194856B2 (en) | 2015-12-22 | 2019-02-05 | Sharp Laboratories Of America, Inc. | Matrix multi-sensor array |
US9949683B2 (en) | 2015-12-22 | 2018-04-24 | Sharp Laboratories Of America, Inc. | Dual-function active matrix sensor array |
US11141100B2 (en) | 2015-12-23 | 2021-10-12 | Coloplast A/S | Moisture assessment system and method for wound care |
US10463279B2 (en) | 2016-02-19 | 2019-11-05 | Trustees Of Dartmouth College | Movement monitoring systems and methods |
KR102493491B1 (en) | 2016-03-04 | 2023-01-31 | 삼성전자주식회사 | Electric device for measuring biometric information and method for operating the same |
US20190053751A1 (en) | 2016-03-22 | 2019-02-21 | Evelyn TORRES | Smart bed |
US20170311807A1 (en) | 2016-04-27 | 2017-11-02 | Hill-Rom Services, Inc. | Apparatuses for detecting biomarkers and methods for using the same |
EP3435850B1 (en) | 2016-04-29 | 2024-06-05 | LifeLens Technologies, Inc. | Monitoring and management of physiologic parameters of a subject |
WO2017214188A1 (en) | 2016-06-06 | 2017-12-14 | University Of Massachusetts | Systems and methods for prevention of pressure ulcers |
WO2017218818A2 (en) | 2016-06-15 | 2017-12-21 | Cvr Global, Inc. | Method for eliminating noise in signal data from a piezoelectric device and detecting stenosis |
WO2018009912A1 (en) | 2016-07-07 | 2018-01-11 | The Regents Of The University Of California | Implants using ultrasonic waves for stimulating tissue |
KR101776698B1 (en) | 2016-08-12 | 2017-09-11 | 연세대학교 산학협력단 | Capacitance bio sensor for identification of bacteria and antibiotics susceptibility test |
WO2018071715A1 (en) | 2016-10-13 | 2018-04-19 | Masimo Corporation | Systems and methods for patient fall detection |
US20200008299A1 (en) | 2016-10-21 | 2020-01-02 | Bao Tran | Flexible printed electronics |
GB2596469B (en) | 2016-10-28 | 2022-03-23 | Tridonic Gmbh & Co Kg | Lighting device |
WO2018115461A1 (en) | 2016-12-22 | 2018-06-28 | Fleming Medical Ltd. | A dressing system |
BR112019008567A2 (en) | 2017-02-03 | 2019-09-10 | Bruin Biometrics Llc | apparatus for identifying injured tissue and method for identifying damaged tissue |
GB2591708B (en) | 2017-02-03 | 2021-11-17 | Bruin Biometrics Llc | Measurement of susceptibility to diabetic foot ulcers |
GB2600267B (en) | 2017-02-03 | 2022-11-23 | Bruin Biometrics Llc | Measurement of tissue viability |
JP6900477B2 (en) | 2017-02-03 | 2021-07-07 | ブルーイン、バイオメトリクス、リミテッド、ライアビリティー、カンパニーBruin Biometrics, Llc | A device for assessing compartment syndrome and a computer-readable medium for detecting compartment syndrome |
GB201800057D0 (en) | 2018-01-03 | 2018-02-14 | Smith & Nephew Inc | Component Positioning And stress Relief For Sensor Enabled Wound Dressings |
WO2018209100A1 (en) | 2017-05-10 | 2018-11-15 | Northwestern University | Functional fabric devices having integrated sensors |
CN110870021A (en) | 2017-05-15 | 2020-03-06 | 史密夫及内修公开有限公司 | Negative pressure wound therapy system using Euler video amplification |
AU2018288530B2 (en) | 2017-06-23 | 2024-03-28 | Smith & Nephew Plc | Positioning of sensors for sensor enabled wound monitoring or therapy |
GB201803496D0 (en) | 2018-03-05 | 2018-04-18 | Smith & Nephew | Skewing pads for impedance measurement |
AU2018312883A1 (en) | 2017-08-10 | 2020-02-20 | Smith & Nephew Plc | Positioning of sensors for sensor enabled wound monitoring or therapy |
GB201804971D0 (en) | 2018-03-28 | 2018-05-09 | Smith & Nephew | Electrostatic discharge protection for sensors in wound therapy |
JP2020533093A (en) | 2017-09-10 | 2020-11-19 | スミス アンド ネフュー ピーエルシーSmith & Nephew Public Limited Company | Systems and methods for inspecting encapsulation, as well as components within wound dressings equipped with sensors |
GB201718870D0 (en) | 2017-11-15 | 2017-12-27 | Smith & Nephew Inc | Sensor enabled wound therapy dressings and systems |
WO2019072531A1 (en) | 2017-09-28 | 2019-04-18 | Smith & Nephew Plc | Neurostimulation and monitoring using sensor enabled wound monitoring and therapy apparatus |
EP3694463A4 (en) | 2017-10-10 | 2021-08-04 | Stryker Global Technology Center PVT. Ltd. | Patient monitoring system and method thereof |
GB201718851D0 (en) | 2017-11-15 | 2017-12-27 | Smith & Nephew | Flocked conformable circuit boards for sensor enabled wound therapy dressings and systems |
JP6995574B2 (en) | 2017-11-10 | 2022-01-14 | 日本航空電子工業株式会社 | connector |
JP2021502845A (en) | 2017-11-15 | 2021-02-04 | スミス アンド ネフュー ピーエルシーSmith & Nephew Public Limited Company | Integrated sensor-enabled wound monitoring and / or treatment coverings and systems |
CN116473517A (en) | 2017-11-16 | 2023-07-25 | 布鲁恩生物有限责任公司 | Strategic treatment of pressure ulcers using subsurface moisture values |
WO2019113481A1 (en) | 2017-12-07 | 2019-06-13 | Bruin Biometrics, Llc | Sem trend analysis |
GB2584226B (en) | 2018-02-09 | 2022-06-22 | Bruin Biometrics Llc | Detection of tissue damage |
WO2019162272A1 (en) | 2018-02-21 | 2019-08-29 | T.J.Smith And Nephew, Limited | Monitoring of body loading and body position for the treatment of pressure ulcers or other injuries |
US11504071B2 (en) | 2018-04-10 | 2022-11-22 | Hill-Rom Services, Inc. | Patient risk assessment based on data from multiple sources in a healthcare facility |
CN208111467U (en) | 2018-05-24 | 2018-11-16 | 山西国惠光电科技有限公司 | A kind of infrared array detector novel package structure |
US11266345B2 (en) | 2018-07-16 | 2022-03-08 | Swift Medical Inc. | Apparatus for visualization of tissue |
EP3603492B1 (en) | 2018-08-01 | 2021-06-16 | Hill-Rom Services, Inc. | Systems for patient turn detection and confirmation |
GB201814011D0 (en) | 2018-08-29 | 2018-10-10 | Smith & Nephew | Componet positioning and encapsulation for sensor enabled wound dressings |
GB2592508B (en) | 2018-09-12 | 2022-08-31 | Smith & Nephew | Device, apparatus and method of determining skin perfusion pressure |
GB2591711B (en) | 2018-10-11 | 2022-02-02 | Bruin Biometrics Llc | Device with detachable element |
US11406286B2 (en) | 2018-10-11 | 2022-08-09 | Masimo Corporation | Patient monitoring device with improved user interface |
US20200296821A1 (en) | 2019-03-11 | 2020-09-17 | Signify Holding B.V. | Reducing Capacitive Coupling On Metal Core Boards |
JP2022525859A (en) | 2019-03-18 | 2022-05-20 | スミス アンド ネフュー ピーエルシー | Design rules for sensor integrated boards |
WO2020190549A1 (en) | 2019-03-18 | 2020-09-24 | Purdue Research Foundation | Omniphobic paper-based smart bandage devices |
US20220151506A1 (en) | 2019-03-19 | 2022-05-19 | Smith & Nephew Plc | Systems and methods for measuring tissue impedance |
CN113710153A (en) | 2019-05-23 | 2021-11-26 | T.J.史密夫及内修有限公司 | System and method for monitoring and treating diabetic foot ulcers |
AU2020103438A4 (en) | 2020-11-13 | 2021-01-28 | Nijhawan, Parag MR | A face shield for sensing body temperature and oxygen level |
IL305699A (en) | 2021-03-09 | 2023-11-01 | Bruin Biometrics Llc | Method for diagnosis and treatment of deep tissue injury using sub-epidermal moisture measurements |
-
2011
- 2011-05-06 PL PL19190000.0T patent/PL3581105T3/en unknown
- 2011-05-06 AU AU2011253253A patent/AU2011253253B2/en active Active
- 2011-05-06 JP JP2013509311A patent/JP5763751B2/en active Active
- 2011-05-06 EP EP22172497.4A patent/EP4122383A1/en active Pending
- 2011-05-06 SI SI201132070T patent/SI3581105T1/en unknown
- 2011-05-06 EP EP16169670.3A patent/EP3078324A1/en not_active Ceased
- 2011-05-06 PT PT117810614T patent/PT2569618T/en unknown
- 2011-05-06 KR KR1020167033760A patent/KR101809623B1/en active IP Right Grant
- 2011-05-06 EP EP23207316.3A patent/EP4335362A1/en active Pending
- 2011-05-06 EP EP16196899.5A patent/EP3155965A1/en active Pending
- 2011-05-06 ES ES11781061.4T patent/ES2626143T3/en active Active
- 2011-05-06 CN CN201180027702.3A patent/CN102933958B/en active Active
- 2011-05-06 WO PCT/US2011/035618 patent/WO2011143071A2/en active Application Filing
- 2011-05-06 HU HUE19190000A patent/HUE059711T2/en unknown
- 2011-05-06 BR BR122021016044-9A patent/BR122021016044B1/en active IP Right Grant
- 2011-05-06 LT LTEP19190000.0T patent/LT3581105T/en unknown
- 2011-05-06 DK DK19190000.0T patent/DK3581105T3/en active
- 2011-05-06 SG SG2012081691A patent/SG185131A1/en unknown
- 2011-05-06 CA CA3190351A patent/CA3190351A1/en active Pending
- 2011-05-06 CA CA2811609A patent/CA2811609C/en active Active
- 2011-05-06 PT PT191900000T patent/PT3581105T/en unknown
- 2011-05-06 BR BR112012028408A patent/BR112012028408B8/en active IP Right Grant
- 2011-05-06 EP EP19190000.0A patent/EP3581105B1/en active Active
- 2011-05-06 CA CA3082134A patent/CA3082134C/en active Active
- 2011-05-06 ES ES19190000T patent/ES2927727T3/en active Active
- 2011-05-06 BR BR122021014110-0A patent/BR122021014110B1/en active IP Right Grant
- 2011-05-06 KR KR1020127031008A patent/KR101688918B1/en active IP Right Grant
- 2011-05-06 EP EP11781061.4A patent/EP2569618B1/en active Active
-
2012
- 2012-11-02 US US13/668,047 patent/US20130123587A1/en not_active Abandoned
-
2013
- 2013-08-05 HK HK13109075.4A patent/HK1181847A1/en unknown
-
2014
- 2014-06-06 US US14/297,977 patent/US9220455B2/en active Active
-
2015
- 2015-06-10 JP JP2015117500A patent/JP5978352B2/en active Active
- 2015-08-17 US US14/827,375 patent/US9398879B2/en active Active
-
2016
- 2016-03-02 US US15/058,964 patent/US9980673B2/en active Active
- 2016-04-09 US US15/095,046 patent/US10188340B2/en active Active - Reinstated
- 2016-07-21 JP JP2016143702A patent/JP2016198547A/en active Pending
-
2018
- 2018-08-01 JP JP2018145355A patent/JP6574030B2/en active Active
- 2018-12-05 US US16/210,911 patent/US11253192B2/en active Active
-
2019
- 2019-06-13 US US16/440,687 patent/US11779265B2/en active Active
-
2023
- 2023-06-30 US US18/346,103 patent/US20230337966A1/en active Pending
Patent Citations (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5152296A (en) * | 1990-03-01 | 1992-10-06 | Hewlett-Packard Company | Dual-finger vital signs monitor |
US20020032485A1 (en) * | 2000-03-29 | 2002-03-14 | Eric Flam | Apparatus and methods for preventing and/or healing pressure ulcers |
US20070051362A1 (en) * | 2004-04-23 | 2007-03-08 | Sullivan Timothy R | Multiple unit dose drug delivery system |
US20060239547A1 (en) * | 2005-04-20 | 2006-10-26 | Robinson M R | Use of optical skin measurements to determine cosmetic skin properties |
US20070185392A1 (en) * | 2005-09-02 | 2007-08-09 | Sherman Faiz F | Method and device for indicating moisture content of skin |
US20090306487A1 (en) * | 2006-04-11 | 2009-12-10 | The University Of Nottingham | Photoplethysmography |
US20080054276A1 (en) * | 2006-08-31 | 2008-03-06 | Fraunhofer-Gesellschaft Zur Forderung Der Angerwandten Forschung E.V. | Reflex coupler with integrated organic light emitter |
US20080063363A1 (en) * | 2006-08-31 | 2008-03-13 | Georgia Tech Research | Method and computer program product for synchronizing, displaying, and providing access to data collected from various media |
US20080166268A1 (en) * | 2007-01-10 | 2008-07-10 | Hiroshi Yamaguchi | Test sheet, apparatus, method and program for diagnosing an object |
US20090054752A1 (en) * | 2007-08-22 | 2009-02-26 | Motorola, Inc. | Method and apparatus for photoplethysmographic sensing |
Non-Patent Citations (4)
Title |
---|
Arimoto et al. (Non-contact Skin Moisture Measurement Based on Near-Infrared Spectroscopy, Applied Spectroscopy Vol. 58, Issue 12, pp. 1439-1446 (Year: 2004) * |
Avci et al., "Low-Level Laser (Light) Therapy (LLLT) in Skin: Stimulating, Healing, Restoring", Seminars in Cutaneous Medicine and Surgery 32(1):41-52 (Year: 2013) * |
Bates-Jensen et al., "Subepidermal moisture is associated with early pressure ulcer damage in nursing home residents with dark skin tones: pilot findings." J Wound Ostomy Continence Nurs., May-Jun;36(3):277-84 (Year: 2009) * |
Gladshtein et al, WO2011048556A2 Abstract (Year: 2011) * |
Also Published As
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US20230337966A1 (en) | SEM Scanner Sensing Apparatus, System and Methodology for Early Detection of Ulcers | |
AU2018204664B2 (en) | SEM scanner sensing apparatus, system and methodology for early detection of ulcers |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STPP | Information on status: patent application and granting procedure in general |
Free format text: NON FINAL ACTION MAILED |
|
AS | Assignment |
Owner name: BRUIN BIOMETRICS, LLC, CALIFORNIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:FLESCH, MICHAEL;BOYSTAK, JOSEPH;REEL/FRAME:065255/0759 Effective date: 20111221 Owner name: THE REGENTS OF THE UNIVERSITY OF CALIFORNIA, CALIFORNIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:SARRAFZADEH, MAJID;KAISER, WILLIAM;MEHRNIA, ALIREZA;AND OTHERS;SIGNING DATES FROM 20121111 TO 20121221;REEL/FRAME:065255/0682 |
|
STPP | Information on status: patent application and granting procedure in general |
Free format text: RESPONSE TO NON-FINAL OFFICE ACTION ENTERED AND FORWARDED TO EXAMINER |
|
STPP | Information on status: patent application and granting procedure in general |
Free format text: NON FINAL ACTION MAILED |
|
STPP | Information on status: patent application and granting procedure in general |
Free format text: RESPONSE TO NON-FINAL OFFICE ACTION ENTERED AND FORWARDED TO EXAMINER |
|
STPP | Information on status: patent application and granting procedure in general |
Free format text: FINAL REJECTION MAILED |