A material that includes a polymer foam and at least one polar dopant molecule included in the polymer foam, wherein the material is a piezoelectric.

The present invention discloses a flexible sensor detection system for medical care and health, including: an information collection module, which uses a wearable device as a carrier, where flexible sensors are respectively arranged on the wearable device; an information transmission module, configured to wirelessly transmit collected information to an information processing and feedback module; and the information processing and feedback module, configured to perform grading treatment on received data information and feed back a health condition corresponding to the data information to the information transmission module, where the information transmission module compares feedback health condition data with a preset health threshold to determine whether to give an alarm. A heart rate ECG band, a breathing band, a shell temperature band, a blood flow rate band, a blood glucose band, a blood oxygen band, and a deep temperature band of the present invention are provided with the built-in flexible sensors.

The present invention provides: a piezoelectric substrate which includes a first piezoelectric body having an elongated shape and helically wound in one direction, and which does not include a core material, in which the first piezoelectric body includes a helical chiral polymer (A) having an optical activity; in which the length direction of the first piezoelectric body is substantially parallel to the main direction of orientation of the helical chiral polymer (A) included in the first piezoelectric body; and in which the first piezoelectric body has a degree of orientation F, as measured by X-ray diffraction according to the following Equation (a), within the range of 0.5 or more but less than 1.0:
degree of orientation F=(180°−α)/180°  (a)
(in which α represents the half-value width of the peak derived from the orientation).

The present invention provides: a piezoelectric substrate which includes a first piezoelectric body having an elongated shape and helically wound in one direction, and which does not include a core material, in which the first piezoelectric body includes a helical chiral polymer (A) having an optical activity; in which the length direction of the first piezoelectric body is substantially parallel to the main direction of orientation of the helical chiral polymer (A) included in the first piezoelectric body; and in which the first piezoelectric body has a degree of orientation F, as measured by X-ray diffraction according to the following Equation (a), within the range of 0.5 or more but less than 1.0:
degree of orientation F=(180°−α)/180°  (a)
(in which α represents the half-value width of the peak derived from the orientation).

Aspects of the present disclosure describe systems, methods, and structures that scavenge mechanical energy to provide electrical energy to a wearable, where the mechanical energy is scavenged by a bending-strain-based transducer that includes a non-resonant energy harvester. By employing a non-resonant energy harvester that operates in bending mode, more electrical energy can be generated that possible with prior-art energy harvesters. In some embodiments the bending-strain-based transducer also includes a sensor and/or a haptic device. Some transducers in accordance with the present disclosure comprise a piezoelectric layer comprising a low-K piezoelectric material, such as aluminum nitride, which enables generation of higher voltage and power/energy output and/or a thinner transducer. As a result, transducers in accordance with the present disclosure can be included in wearables for which large transducer thickness would be problematic, such as sole members (e.g., shoe insoles, midsoles or outsoles), garments, bras, handbags, backpacks, and the like.

This invention describes a type of all-organic piezoelectric material based on cellulose nanocrystals (CNCs). This type of material is flexible and transparent, and its properties can be tuned by adjusting the composition and ionic strength. The fabrication of this type of piezoelectric material can be carried out entirely in an aqueous medium and does not require high temperature poling and stretching treatment. It renders possible a commercially viable route to producing inexpensive, sustainable, eco-friendly high piezo-electric-response organic materials for sensors, transducers, actuators, and energy harvest applications.

A photocurable resin may comprise piezonanoparticles. The piezonanoparticles may comprise functionalized barium titanate (f-BTO), functionalized lead zirconate titanate (f-PZT), or functionalized aluminum nitride (f-AlN). The photocurable resin may further comprise a photo-initiator, a photo-absorber, or PEGDA 700.

A photocurable resin may comprise piezonanoparticles. The piezonanoparticles may comprise functionalized barium titanate (f-BTO), functionalized lead zirconate titanate (f-PZT), or functionalized aluminum nitride (f-AlN). The photocurable resin may further comprise a photo-initiator, a photo-absorber, or PEGDA 700.

At least one silicone layer is applied to a substrate by a method employing laser transfer printing. The method is suitable for producing sensors, actuators and other EAP layer systems. The silicone layer in these systems may serve as an electrically conducting electrode layer or as a dielectric layer. The method may be configured to be continuous and may be combined with various other coating technologies.

To provide a piezoelectric body film that can suppress decrease in the piezoelectric constant d31, a method of producing a piezoelectric body film, and a piezoelectric body device. A piezoelectric body film comprising a fluororesin as a piezoelectric material, the fluororesin containing, as a main constituent unit, a repeating unit derived from vinylidene fluoride, a piezoelectric constant d31 of the piezoelectric body film being 20 pC/N or greater, and an extrapolated onset temperature at start of shrinkage determined by TMA measurement being not lower than 90° C. and not higher than 115° C. The difference between piezoelectric constants d31 measured before and after heating the piezoelectric body film at 100° C. for 24 hours relative to the piezoelectric constant d31 before the heating for 24 hours is 20% or less.