Standardized bilirubin phototherapy system

Abstract

A standardized phototherapy system for delivering a controlled dose of therapeutic light within a therapeutic optical bandwidth to a patient. The phototherapy system includes a therapeutic light source configured to generate spatially uniform irradiance over is a treatment region. The irradiance generated over the treatment region is controlled by controller via a driver signal and is calibrated using a photonic dosimeter matched to the therapeutic light source. The photonic dosimeter is a photonic dosimeter configured to establish a reference relationship between the driver signal provided to the therapeutic light source and the irradiance generated over the treatment region. The controller can adjust the irradiance of the therapeutic light over the therapy region based on patient data comprising measured concentration of a biological analyte in patient's blood.

Description

METSE.OOIWO PATENTSTANDARDIZED BILIRUBIN PHOTOTHERAPY SYSTEMINCORPORATION BY REFERENCE TO ANY PRIORITY APPLICATIONS

[0001] This application claims the benefit of priority to U.S. Provisional Appl. No. 63 / 724,556 titled “STANDARDIZED BILIRUBIN PHOTOTHERAPY SYSTEM” filed on November 25, 2024, which is incorporated in its entirety by reference herein.FIELD OF THE DISCLOSURE

[0002] The present disclosure relates to phototherapy systems for controlled delivery of therapeutic light to a patient. In particular phototherapy systems that delivers standardized uniform therapeutic light to a neonatal patient for treatment of hyperbilirubinemia.BACKGROUND

[0003] Phototherapy is a therapeutic technique that uses specific wavelengths of light to treat certain medical conditions. It is widely employed in treating various medical conditions such as skin disorders, pain management, wound healing, mental health, and the like. Phototherapy is a critical treatment for neonatal jaundice, a condition caused by elevated bilirubin levels in newborns. By exposing the infant’s skin to specific wavelengths of light, phototherapy converts bilirubin into water-soluble forms that can be easily excreted by the body. This non-invasive therapy significantly reduces the risk of severe complications such as kemicterus, which can lead to brain damage. Modern phototherapy systems are designed for efficiency, portability, and precise light delivery, ensuring optimal outcomes while maintaining safety for the infant.SUMMARY

[0004] In some aspects, the techniques described herein relate to a system for providing bilirubin phototherapy to a treatment region of a pediatric patient, the systemincluding: a light box including a plurality of illumination units arranged in a matrix and an output window configured to cover output apertures of the plurality of illumination units, wherein each of the plurality of illumination units includes: at least one light emitting diode (LED), configured to emit therapeutic light within a therapeutic bandwidth around a peak therapeutic wavelength; and an optical reflector configured to reflect at least a portion of the therapeutic light emitted by the at least one LED, wherein the optical reflector is configured to reflect the therapeutic light towards the output window, wherein the output window has a reflectance greater than or equal to 50% at the peak therapeutic wavelength; a photonic dosimeter configured to be positioned in proximity to the treatment region or an expected treatment region, wherein the photonic dosimeter is configured to generate an irradiance signal indicative of irradiance of a portion of the emitted therapeutic light incident on the treatment region or an expected treatment region, the photonic dosimeter including: a second LED configured to generate a sensor signal in response to receiving the portion of the emitted therapeutic light, wherein the second LED is substantially identical to the at least one LED; and a readout circuit including an averaging circuit, the readout circuit configured to receive the sensor signal and generate the irradiance signal based on the sensor signal; and a controller configured to generate a driver signal, the driver signal configured to control irradiance of the emitted therapeutic light, wherein the irradiance of the emitted light is calibrated based on the irradiance signal.

[0005] In some embodiments, the irradiance of the emitted light is calibrated based on the irradiance signal during a calibration period by measuring another irradiance of the emitted light, during the calibration period, using the photonic dosimeter and independently using a calibrated spectroradiometer (e.g., a calibrated optical spectrum analyzer), comparing a test irradiance signal generated by the photonic dosimeter in response to receiving therapeutic light with a reference irradiance signal generated by the calibrated spectroradiometer in response to receiving the same therapeutic light, and deriving the calibration data based on the comparison. In some cases, the irradiance of the irradiance of the emitted light or the therapeutic light may comprise one or more of a peak irradiance (e.g., peak spectral irradiance) and total irradiance.

[0065] In some cases, the second LED can be substantially identical to the at least one LED when one or both the peak emission wavelength (e.g., a center wavelength) andbandwidth (e.g., full-width-half-max) of the emission of the second LED is substantially identical to those of the at least one LED. A peak emission wavelength of the second LED can be within ± 1%, within ± 2%, within ± 4%, within ± 5%, within ± 7%, of a peak emission wavelength of the at least one LED. A bandwidth of light emitted by the second LED can be within ± 1%, within ± 2%, within ± 4%, within ± 5%, within ± 7%, of a bandwidth of light emitted by the at least one LED.

[0007] In some aspects, the techniques described herein relate to a system, further including at least one driver configured to receive the driver signal and provide a drive current to the at least one LED to generate the therapeutic light.

[0008] In some aspects, the techniques described herein relate to a system, wherein the driver signal is pulse width modulated signal having a duty cycle, and wherein the irradiance of the light is controlled by the duty cycle.

[0009] In some aspects, the techniques described herein relate to a system, wherein the at least one driver includes first and second drives configured to provide first and second driver signals to first and second illumination units of the plurality of illumination units, respectively, wherein a difference between the first and second driver signal is configured to reduce a spatial variation of the irradiance over the treatment region or the expected treatment region.

[0010] In some aspects, the techniques described herein relate to a system, wherein the controller is further configured to: determine an irradiance value based on the driver signal, a normal distance between the output window and the treatment region or the expected treatment region, and calibration data stored in a non-transitory memory, and display the irradiance value on a user interface, wherein the calibration data includes a reference relationship between the driver signal and a measured irradiance at the normal distance.

[0011] In some aspects, the techniques described herein relate to a system, wherein the user interface is a touch sensitive display.

[0012] In some aspects, the techniques described herein relate to a system, wherein the calibration data is generated using the irradiance signal during a calibration period.

[0013] In some aspects, the techniques described herein relate to a system, wherein the normal distance is provided by a user via the user interface.

[0014] In some aspects, the techniques described herein relate to a system, wherein the system is in wired or wireless communication with a computing system including the user interface.

[0015] In some aspects, the techniques described herein relate to a system, wherein the computing system includes laptop, a tablet, a personal computer, or a smartphone.

[0016] In some aspects, the techniques described herein relate to a system, wherein the photonic dosimeter does not include a narrow-band optical filter.

[0017] In some aspects, the techniques described herein relate to a system, wherein a reflecting surface of the reflector includes a reflective coating configured to reflect at least 95% of the received portion of the therapeutic light.

[0018] In some aspects, the techniques described herein relate to a system, wherein the reflector includes a parabolic or hemispherical reflector.

[0019] In some aspects, the techniques described herein relate to a system, wherein the peak therapeutic wavelength is between 470 nm and 480 nm.

[0020] In some aspects, the techniques described herein relate to a system, wherein the peak therapeutic wavelength is about 475 nm.

[0021] In some aspects, the techniques described herein relate to a system, wherein the therapeutic bandwidth is less than 25 nm.

[0022] In some aspects, the techniques described herein relate to a system, wherein the therapeutic bandwidth is from 18 nm to 24 nm.

[0023] In some aspects, the techniques described herein relate to a system, wherein the controller is in wired or wireless communication with a computing system, the computing system including a non-transitory memory storing machine-readable instructions and a hardware processor configured to execute the machine-readable instructions to: receive patient data a user or a remote computing system via a wired or wireless link; determine a target irradiance based on the patient data; and control the driver signal to deliver the target irradiance to treatment region, wherein the patient data is associated with the pediatric patient.

[0024] In some aspects, the techniques described herein relate to a system, wherein the hardware processor is further configured to determine a target phototherapy time based on the patient data and control the driver signal to deliver the target irradiance during the determined target phototherapy time.

[0025] In some aspects, the techniques described herein relate to a system, wherein the remote computing system includes a medical record system.

[0026] In some aspects, the techniques described herein relate to a system, wherein the patient data includes one or more of a biochemical parameter of the pediatric patient, a physical parameter of the pediatric patient, and a physiological parameter of the pediatric patient.

[0027] In some aspects, the techniques described herein relate to a system wherein the biochemical parameter of the pediatric patient includes a bilirubin level or concentration.

[0028] In some aspects, the techniques described herein relate to a system, wherein the photonic dosimeter transmits the irradiance signal to the controller via a wired or wireless link.

[0029] In some aspects, the techniques described herein relate to a phototherapy system for providing therapeutic light to a patient, the phototherapy system including: a first light emitting diode (LED) configured to emit the therapeutic light having wavelengths within a therapeutic bandwidth around a peak therapeutic wavelength; and a photonic dosimeter configured to receive the therapeutic light and generate an irradiance signal indicative of irradiance of the therapeutic light, the photonic dosimeter including: a second LED configured to generate a sensor signal in response to receiving the therapeutic light, wherein the second LED is substantially identical to the first LED; and a readout circuit including an averaging circuit, the readout circuit configured to receive the sensor signal and generate the irradiance signal based on the sensor signal.

[0030] In some aspects, the techniques described herein relate to a phototherapy system, wherein the peak therapeutic wavelength is about 475 nm.

[0031] In some aspects, the techniques described herein relate to a phototherapy system, wherein the therapeutic bandwidth is less than 25 nm.

[0032] In some aspects, the techniques described herein relate to a phototherapy system, wherein the at least one LED includes a first PN junction configured to generate the therapeutic light upon receiving electric current and the second LED includes a second PN junction configured to generate the sensor signal upon receiving the therapeutic light, and wherein the first PN junction is substantially identical to the second PN junction.

[0033] In some aspects, a first doping concentration profile and first material composition of the first PN junction can be substantially identical to a second doping concentration profile and second material composition of the second PN junction.

[0034] In some aspects, the techniques described herein relate to a phototherapy system, wherein one or both the peak emission wavelength and bandwidth (e.g., full-widthhalf-max) of the second LED are identical or substantially identical to those of the at least one LED.

[0035] In some aspects, the techniques described herein relate to a photonic dosimeter configured to receive incident light and generate an irradiance signal indicative of irradiance of the light, the photonic dosimeter including: A light emitting diode (LED) configured to generate a sensor signal in response to receiving the incident light; and a readout circuit configured to receive the sensor signal and generate the irradiance signal based on the sensor signal.

[0036] In some aspects, the techniques described herein relate to a photonic dosimeter, wherein the readout circuit includes an averaging circuit.

[0037] In some aspects, the techniques described herein relate to a photonic dosimeter, wherein the received incident light includes wavelengths within a bandwidth around a peak incident wavelength, and wherein upon being driven by an electric current, the LED generates light having a peak emission wavelength within ± 1% of the peak incident wavelength.

[0038] In some aspects, the techniques described herein relate to a photonic dosimeter, wherein the bandwidth of the incident light is less than 25 nm.

[0039] In some aspects, the techniques described herein relate to a photonic dosimeter, wherein the bandwidth of the incident light is less than 50 nm.

[0040] In some aspects, the techniques described herein relate to a photonic dosimeter, wherein the peak incident wavelength is about 475 nm.

[0041] In some aspects, a standardized phototherapy system may deliver controlled dose of therapeutic light within a therapeutic optical band to a patient. The phototherapy system includes a therapeutic light source configured to generate spatially uniform irradiance over a treatment region. The irradiance generated over the treatment region is controlled by a controller via a driver signal and is calibrated using a photonic dosimeter matched to thetherapeutic light source. The photonic dosimeter is a photonic dosimeter configured to establish a reference relationship between the driver signal provided to the therapeutic light source and the irradiance generated over the treatment region. The controller can adjust the irradiance of the therapeutic light over the therapy region based on patient data comprising measured concentration of a biological analyte in patient’s blood.BRIEF DESCRIPTION OF THE DRAWINGS

[0042] FIG. 1 high-level block diagram showing the general configuration of a phototherapy system for providing therapeutic light to a patient, in accordance with certain embodiments of the present disclosure.

[0043] FIG. 2 A illustrates an example phototherapy system configured to provide therapeutic light to a patient in accordance with certain embodiments of the present disclosure.

[0044] FIG. 2B illustrates an example phototherapy system mounted on a rolling stand for bedside phototherapy treatment in accordance with certain embodiments of the present disclosure.

[0045] FIG. 3A illustrates cross-sectional bottom (bottom panel) and side (top panel) views of a therapeutic light source comprising a plurality of illumination units in accordance with certain embodiments of the present disclosure.

[0046] FIG. 3B illustrates orthogonal cross-sectional views of an individual illumination unit of the therapeutic light source shown in FIG. 3A depicting transverse (xz), longitudinal (yz) and horizontal (xy) cross-sections of the illumination unit, in accordance with certain embodiments of the present disclosure.

[0047] FIG. 3C illustrates the measured angular luminous intensity distribution, for an example light emitting unit used in the illumination unit shown in FIG. 3B.

[0048] FIG. 3D illustrates transverse cross-sectional view of an example optical reflector configured to capture and reflect the light emitted from a light emitting element having an emission according to the angular luminous intensity distribution shown to FIG. 3C.

[0049] FIG. 4A illustrates cross-sectional bottom (bottom panel) and side (top panel) views of another therapeutic light source comprising a plurality of illumination units in accordance with certain embodiments of the present disclosure.

[0050] FIG. 4B illustrates orthogonal cross-sectional views of an individual illumination unit of the therapeutic light source shown in FIG. 4A depicting transverse (xz), longitudinal (yz) and horizontal (xy) cross-sections of the illumination unit, in accordance with certain embodiments of the present disclosure.

[0051] FIG. 4C illustrates three-dimensional views of the illumination unit shown in FIG. 4B, and a light box comprising 32 substantially identical illumination units of the type shown in FIG. 4B, arranged in a 4 by 8 matrix.

[0052] FIG. 4D illustrates a cross-sectional bottom view of another example light box formed by six groups of illumination units of the type shown in FIG. 4B.

[0053] FIG. 5A illustrates a three-dimensional schematic diagram of a light source support frame, shown from a top perspective, and a plurality of cooling devices mounted thereon. The light source support frame is configured to house a plurality of illumination units to form a therapeutic light source, e.g., the therapeutic light source shown in FIGS. 2A.

[0054] FIG. 5B illustrates a three-dimensional schematic diagram of the light source support frame in FIG. 5A, shown from a bottom perspective.

[0055] FIG. 5C illustrates an exploded view of a therapeutic light source formed using the light source support frame shown in FIGS 5A and 5B, depicting peripheral components and certain functional accessories of the therapeutic light source. The inset shows a close-up view of a reflector support frame of the light source support frame.

[0056] FIG. 6A is a schematic diagram illustrating a top view (top panel) of a circuit diagram (bottom panel) of a light-emitting element formed by an array of light emitting diodes (LEDs).

[0057] FIG. 6B illustrates a three-dimensional schematic diagram showing the light-emitting element of FIG. 6 A and a heat sink configured for connection to the lightemitting element.

[0058] FIG. 7 A illustrates, measured intensity of light emitted by a therapeutic light source at a peak therapeutic wavelength as a function of the normal distance from the exit aperture of the therapeutic light source.

[0059] FIG. 7B illustrates a nine-point irradiance measurement configuration for measuring the uniformity of therapeutic light generated by light boxes shown in FIG. 3A and 4A over a target region or area on a target surface.

[0060] FIG. 7C illustrates, an example setup for measuring the uniformity of irradiance generated by therapeutic light source.

[0061] FIG. 8 illustrates a circuit diagram depicting a portion of an electronic circuit used to drive and control a therapeutic light source.

[0062] FIG. 9A illustrates a measurement setup used to characterize light emitted by a therapeutic light source with, e.g.. respect to normal distance from the exit aperture of the therapeutic light source.

[0063] FIG. 9B illustrates the measured voltages output by a light measurement system of the measurement setup shown in FIG. 9A, as a function of the duty cycle of the driver signal.

[0064] FIG. 10A illustrates spectral intensity of light emitted by a therapeutic light source (solid curve) and spectral responsivity of a typical photodetector (dashed curve).

[0065] FIG. 10B illustrates spectral intensity of light emitted by a therapeutic light source (solid curve) and spectral responsivity of a photonic dosimeter (dotted curve) that is spectrally matched with the therapeutic light source.

[0066] FIG. 10C illustrates an example circuit for transforming photocurrent generated by a photodiode or an LED used as an optical sensor, upon being illuminated, to an input voltage usable by a control and / or measurement circuit.

[0067] FIGS. 10D -10E illustrate a schematic cross-sectional side view (10D) and a photograph (10E) of an example a photonic dosimeter for control and monitoring therapeutic light generate by a therapeutic light source.

[0068] FIG. 11 illustrates an example measurement system for calibrating a photonic dosimeter used to monitor and / or control optical output power of a therapeutic light source.

[0069] FIG. 12A schematically illustrates a side cross-sectional view of an example experimental setup for illuminating a liquid sample flowing through a cuvette using a calibrated therapeutic light source.

[0070] FIG. 12B schematically illustrates a side cross-sectional view of an example sample circulation system configured to circulate a liquid sample between a cuvette and a sample reservoir.

[0071] FIGS. 13-34 schematically illustrate different screens generated by a computing system configured to receive patient data and determine, control and / or monitor different parameters associated with phototherapy provided to a patient by a phototherapy system.DETAILED DESCRIPTION

[0072] Neonatal phototherapy is the primary treatment for jaundice in newborns, where controlled light exposure converts bilirubin into water-soluble forms for safe elimination. The effectiveness of this therapy depends heavily on precise light delivery, as both the wavelength and optical power directly influence treatment outcomes. Accurate control and measurement of the delivered optical power are critical, yet current phototherapy systems often lack reliable power calibration. One contributing factor is that power meters used for calibration may not consistently measure true output, leading to discrepancies between intended and actual therapeutic dose. Additionally, spatial uniformity of the light across the treatment area is another challenge — uneven illumination can result in suboptimal therapy or localized undertreatment and contribute to inconsistency between measured and delivered optical power. These limitations highlight the need for advanced phototherapy systems with robust power calibration mechanisms and uniform light distribution to ensure safe, effective, and standardized care for neonates.

[0073] According to the American Academy of Pediatrics (AAP), accurately measuring both the wavelength and irradiance delivered by phototherapy devices is essential to ensure effective treatment outcomes for neonatal jaundice. The AAP recommends using narrowband blue-to-green light having a peak emission (e.g., a center wavelength) between 465 nm - 480 nm, with an optimal value near 478 nm (e.g., at 475 nm) and a spectral irradiance from 25 pW / cm2 / nm to 35 pW / cm2 / nm with an optimal values 30 pW / cm2 / nm. In some cases, a narrowband therapeutic light having a bandwidth (e.g., FWHM of a near-Gaussian spectrum) can improve the phototherapy treatments. In some examples, a bandwidth (FWHM) of about 20 nm can be optical because: it can eliminate the high hemoglobin-absorption region (<460 nm), it can capture the shallow bilirubin absorption plateau (465-485 nm), it may minimize tissue absorption and scattering losses, and it matches LED emission spectra used in modern neonatal phototherapy. Moreover, narrow band emission may allow tailoring response of aradiometer (e.g., a radiometer dedicated to measuring irradiance of bilirubin therapy light), with actual therapeutic photon flux, as opposed to blue-light intensity. In some of the embodiments disclosed herein, irradiance of therapeutic light having such narrow bandwidth may be measured using a direct action- spectrum- weighted dosimeter, rather than a broadband irradiance meter. A direct action-spectrum-weighted dosimeter, herein referred to as photonic dosimeter or dosimeter (photonic-bilimeter), may comprise a dedicated optical sensor (e.g., dedicated to a therapeutic light source with a given emission spectrum) having a spectral response substantially matched or identical to the emission spectrum of the therapeutic light, e.g., with respect to peak (or center) wavelength, spectral shape, and / or a bandwidth (e.g., fullwidth-half-max).

[0074] The actual dose of therapeutic light delivered to a patient can be matched to an intended dose by measuring the irradiance of the therapeutic light using a calibrated a light meter designed specifically for the spectral output of the therapeutic light source. Without precise irradiance measurements, the therapeutic dose may be under- or overestimated — potentially compromising safety and efficacy of the phototherapy

[0075] As indicated by AAP, current phototherapy devices from different manufacturers appear to exhibit substantial variation in optical power and spectral bandwidth of the therapeutic light. Moreover, most commercially available radiometers used to measure light dosage (e.g., optical irradiance in pW / cm2 / nm) vary widely in their wavelength response specifications, depending on the manufacturer. These inconsistencies between the light source wavelength and radiometer response introduce significant errors in accurately measuring the delivered light dosage. As a result, clinical healthcare providers often struggle to meet the AAP’s recommended guideline of achieving a recommended dose or determined dose or irradiance (e.g., 30 pW / cm2 / nm) in practical settings

[0076] The methods and systems described herein address the aforementioned challenges by providing a standardized phototherapy system configured for precise optical power delivery, accurate optical power measurement, accurate optical source calibration, and improved spatial uniformity of therapeutic light. Moreover, some of the methods and systems described below enable precise adjustment of the duration of the phototherapy and the irradiance of the therapeutic light based on measured values of biochemical parameters (e.g., bilirubin level) at regular or scheduled intervals to prevent over or under exposure.

[0077] In some embodiments, a standardized phototherapy system may include a therapeutic light source configured to uniformly illuminate a treatment area such that the variation of the irradiance over the treatment area does not exceed a threshold level. The standardized phototherapy system may additionally include a photonic dosimeter (e.g., a dedicated radiometer) for measuring irradiance of the therapeutic light generated by the standardized phototherapy system at a given location (e.g., at or near a surface region where the patient will be positioned during phototherapy). In some embodiments, the photonic dosimeter (e.g., an optical sensor of the photonic dosimeter) may have a spectral response close to the spectral emission of the therapeutic light source to provide accurate irradiance measurements. In some cases, the photonic dosimeter may not include an optical filter (e.g., a bandpass optical filter). In some cases, the photonic dosimeter may be used for routing testing of the therapeutic light source to validate that a display reading accurately reflects the irradiance received by the patient. In some embodiments, the photonic dosimeter may be used to measure irradiances of the therapeutic light in a region where the patient will be positioned during phototherapy for selected values of irradiance (e.g., selected via a user interface of the standardized phototherapy). The measured irradiances may be compared to the selected values of the irradiance to assess the accuracy of the standardized phototherapy system. In some embodiments, the photonic dosimeter may be used to measure irradiance of the therapeutic light before or during a phototherapy session. In some examples, during a phototherapy session, the photonic dosimeter (e.g., an optical probe of the photonic dosimeter) may be placed on or over a region of the patient’s skin (e.g., a skin region of neonatal patient) to measure the irradiance received by the region. In some cases, the photonic dosimeter may be used for real-time irradiance monitoring and / or report irradiance. In some cases, the photonic dosimeter may be used to form a closed loop irradiance control by providing an accurate and reliable feedback signal to a driver of the therapeutic light source. The closed loop irradiance control can adjust and then maintain the irradiance substantially locked to a specified value. In some cases, the photonic dosimeter may be sent to the manufacturer (e.g., every month, every six months, every year, and the like), to evaluate the accuracy of the photonic dosimeter and, if needed, recalibrating the photonic dosimeter with respect to a standardized radiometer of spectroradiometer.

[0078] In various implementations, the standardized phototherapy systems and methods described below may improve in bilirubin clearance time in neonatal patients, reduce or prevent complications caused by under or over exposure, improve consistency and predictability of the of irradiance delivery, and deliver tailored phototherapy solutions for individual patients and across a wide range of clinical settings.

[0079] Although the standardized phototherapy systems described below are mainly designed for bilirubin phototherapy to control and / or prevent neonatal hyperbilirubinemia its underlying technology — featuring uniform light distribution, precise spectral control, and real-time feedback — can offer broad adaptability across multiple domains. In dermatology, these capabilities can enhance phototherapy treatments for conditions such as psoriasis, eczema, acne, and vitiligo, ensuring consistent therapeutic dosing and improved patient outcomes. Similarly, standardized phototherapy systems may be used to accelerate wound healing in diabetic ulcers and burn injuries by promoting tissue regeneration through controlled light exposure. Beyond human healthcare, the standardized phototherapy systems may be used in veterinary applications, particularly in neonatal animal care, where maintaining optimal light parameters can be critical for survival and growth.Phototherapy system

[0080] FIG. 1 high-level block diagram showing the general configuration of a phototherapy system 100 for providing therapeutic light to a patient 124, in accordance with certain embodiments of the present disclosure. In some embodiments, a phototherapy system100 may comprise a therapeutic light source 101. herein referred to as light source 101. and a control and supply unit 102 configured to drive and control the light source 101. In some embodiments, the control and supply unit 102 may comprise a power supply 108, a controller 104, and a driver 106. The power supply 108 may be configured to provide electric power to the driver 106 (e.g., for powering the light source 101) and to the controller 104. The controller 104 may be configured to control a parameter of the light source 101 (e.g., optical output power) by controlling the driver 106. For example, the driver 106 may drive the light source101 based on a driver control signal (e.g., a pulse width modulated signal) received from the controller 104 and the controller 104 may adjust a parameter of the driver control signal to change the optical output power (e.g., an average optical output power) and thereby theirradiance of the therapeutic light 126 at the treatment region (e.g., a body surface region of the patient 124).

[0081] In some embodiments the light source 101 may be configured to uniformly or near uniformly illuminate the treatment region (e.g., a portion of the body surface of the patient 124 facing the light source 101). In some such embodiments, the irradiance of the therapeutic light 126 over the treatment region can be substantially constant (e.g., within a predefined tolerance range.). In some cases, the irradiance of the therapeutic light 126 over the treatment region may not change more than a threshold level. For example, the irradiance of the therapeutic light 126 can change less than 10 pW / cm2 / nm, less than 8 pW / cm2 / nm, less than 6 pW / cm2 / nm, less than 4 pW / cm2 / nm, or less than 2 pW / cm2 / nm, over the treatment region. In some cases, the treatment region can be a normal projection of a portion of the patient’s body surface facing the light source 101 on a plane substantially parallel to an output aperture of the light source 101. In some such examples, the area of the treatment region can be from 10 to 100 cm2, from 100 to 200 cm2, from 200 to 500 cm2, from 500 to 700 cm2, from 700 to 1000 cm2, from 1000 to 1300 cm2, from 1300 cm2to 1500 cm2, from 15002to 1800 cm2, from 1800 cm2to 2000 cm2, or any ranges formed by these values or larger or smaller values.

[0082] In some embodiments, the light source may emit therapeutic light 126 having wavelengths within a narrow bound around a peak emission wavelength (Xc). In some cases, e.g., when the emission spectrum is nearly symmetric, the peak emission wavelength can be a center wavelength. In some examples, the therapeutic light 126 may have a Gaussian or near Gaussian spectral intensity distribution. In various implementations, kccan be from 460 nm to 465 nm, from 465 nm to 470 nm, from 470 nm to 475nm, from 475 nm to 480 nm, from 480 nm to 485 nm, from 485 nm to 490 nm, or any ranges formed by these values or larger or smaller values.

[0083] In some embodiments, the phototherapy system 100 may operate as a standalone unit equipped with its own user interface 112, such as a display (e.g., a touch- sensitive screen). In some embodiments, the phototherapy system 100 may be in communication with a computing system 114 (e.g., a portable computing system such as a laptop, a smartphone, a tablet, and the like), e.g., via hardware interface 110. In some such embodiments, the computing system 114 may be configured to control the phototherapysystem 100 (e.g., an irradiance of therapeutic light 126 provided by the light source 101 ) automatically or based on an input received from an operator 120.

[0084] In some embodiments, at least the light source 101 can be integrated with the control and supply unit 102 within a common housing to form the phototherapy system 100.

[0085] In some embodiments, the phototherapy system may comprise a photonic dosimeter 122 (also referred to as photonic -bilimeter), for measuring the irradiance provided by the light source 101 at a location (e.g., near or at the treatment region). In some embodiments, the photonic dosimeter 122 can be a dedicated radiometer such as a radiometer spectrally matched to the light source 101). In some cases, the photonic dosimeter 122 may be used by the operator 120 to measure the irradiance generated by the light source 101 on a target surface 127 where the patient will be positioned during therapy. In some cases, the photonic dosimeter 122 may comprise a self-contained radiometer comprising a control panel and a display for reading measured values of irradiance. In some cases, the photonic dosimeter 122 may comprise an optical sensor electrically connected to an electronic measurement device or a computing system 114 (e.g., a personal computer, a laptop, a smartphone, and notepad and the like). In some such cases, the measured values of irradiance may be displayed on a display of the computing system 114. In some cases, the optical sensor of the photonic dosimeter 122 may be electrically connected to the control and supply unit 102 and the measured values of irradiance may be displayed on a display of a user interface 112 of the control and supply unit 102. In some cases, the optical sensor may be electrically connected to the computing system 114 via the control and supply unit 102 and the measured values of irradiance may be displayed on the display of computing system 114. In some embodiments, the photonic dosimeter 122 can be connected to or in communication with the controller 104 via a wired or wireless link. In some cases, the wireless link can be a short-range wireless link.

[0086] In some embodiments, the photonic dosimeter 122 can be a photonic dosimeter calibrated with respect to the light source 101 (e.g., the spectrum of the therapeutic light 126) without using an optical filter (e.g., a narrow band and / or a bandpass optical filter having a bandwidth close or matched to that of the light source 101). In some cases, the photonic dosimeter may compromise an averaging circuit and an optical sensor having a spectral response close or substantially identical to the emission spectrum of the light source101 (e.g., one or more light emitting diodes). In some cases, the optical sensor can be a semiconductor junction that can generate current upon illumination. For example, the optical sensor can be photodiode or an LED used as an optical sensor to detect light. In some cases, one or both the peak emission wavelength (e.g. a center wavelength) and the bandwidth of the LED used as optical sensor can be identical or substantially identical to those of an LED used in the light source 101 to generate therapeutic light. Advantageously, in some cases, when such LED is used as optical sensor, the photonic dosimeter may not include an optical filter (e.g., a bandpass optical filter) to eliminate light wavelength outside of the emission band of the therapeutic light.

[0087] In some cases, the photonic dosimeter may serve as a transfer standard and can be utilized to calibrate the phototherapy system 100. To maintain accuracy, the photonic dosimeter may undergo annual calibration at a calibration and testing facility (e.g., National Institute of Standards and Technology (NIST)-traceable metrology laboratory), where its spectral response and power measurements may be verified against a spectroradiometer.

[0088] In some embodiments, the electronic system may receive an irradiance signal from the photonic dosimeter 122 and control the light source 101 based at least in part on the irradiance signal.

[0089] In some cases, the computing system 114 may receive signal and / or data from the phototherapy system 100 indicative of a measured or expected irradiance provided by the therapeutic light 126 to the treatment region. For example, when the computing system 114 receives a signal from the photonic dosimeter 122, it may display a measured value of the irradiance on the treatment region. In some cases, the computing system 114 may receive a signal from the controller 104, the signal indicating a driver signal provided by the controller 104 to the driver 106, determine an expected value of the irradiance on the target surface 127, and display or report the determined value. For example, when the phototherapy system 100 is calibrated, the controller 104 or the computing system 114 may store calibration data indicative of relation / correspondence between driver signal provided by the controller 104 to the driver 106 and the measured value of the irradiance on target surface 127 for predefined values of vertical distance (h) between the light source 101 and the target surface 127. Upon receiving the signal indicative of the driver signal, the computing system 114 may determine and display the expected value of the irradiance on the target surface 127. Similarly, in somecases, when the phototherapy system 100 is calibrated, the controller 104 may determine and display, an expected value of the irradiance on target surface 127 in a display of the user interface 112 (based on the driver signal sent to the driver 106 and the calibration data.

[0090] In some embodiments, an internal light meter or a light meter sensor can be integrated in the light source 101 to receive (e.g., internally receive) a portion of the therapeutic light 126 generated by the light source 101. In some such embodiments, the controller 104 or the computing system 114 may store another calibration data indicative of relation / correspondence between a signal generated by the internal light meter or a light meter sensor and the measured value of the irradiance on target surface 127 for predefined values of vertical distance (h) between the light source 101 and the target surface 127. In these embodiments, the. the controller 104 or the computing system 114 may receive the signal generated by the internal light meter or an light meter sensor and use the calibration data to determine the and display, an expected value of the irradiance on target surface 127 in a display of the user interface 112 or a display of the computing system 114, respectively.

[0091] In some embodiments, the photonic dosimeter 122 may be used to measure irradiance of the therapeutic light 101 on the target surface 127 for a set irradiance value (e.g., selected via the user interface 112 or a user interface of the computing system 114, or received from the computing system 114). The measured irradiances may be compared to the selected values of the irradiance to assess the accuracy of the phototherapy system 100. In some embodiments, the photonic dosimeter may be used to measure irradiance of the therapeutic light 101 before or during a phototherapy session. In some examples, during a phototherapy session, the photonic dosimeter 122 (e.g., an optical probe of the photonic dosimeter 122) may be placed on or over a region of the patient’s skin (e.g., a skin region of neonatal patient 124) to measure the irradiance received by the region. In some cases, the photonic dosimeter 122 may be electrically connected to the controller 104 of the control and supply unit 102 to form a feedback loop to set and lock the irradiance measured by the photonic dosimeter 122 to a set value stored in or determined by the controller 104 or in the computing system 114. In some cases, the set irradiance value may be provided by the operator 120 via the user interface 112 of phototherapy system 100 or the computing system 114. hi some other cases, the controller 104 or in the computing system 114 may determine the set irradiance value based on patient data provided by the operator 120 or directly received from another system. In some cases, thepatient data may comprise a measured biochemical parameter (e.g., bilirubin level) of the patient 124, other physical or physiological parameters of patient (e.g., weight, gestational age, weight) height, body mass index, skin tone / color, and the like). In some cases, the computing system 114 may be in communication with a medical record system 116 and directly receive biochemical parameters and / or physical parameters of the patient 124 from the medical record system 116. In some embodiments, a biochemical parameter of the patient 124 may be measured (e.g., invasively or non-invasively) at scheduled or regular intervals during a phototherapy period and entered to the computing system 114 or the medical record system 116. Upon receiving the updated biochemical parameter, the computing system 114 may determine an updated level of irradiance and adjust the light source 101 using the controller 104 to change the measured irradiance or expected irradiance of the therapeutic light delivered to the patient 124 to the updated value. Thus, continuous provision of updated patient data — via a user interface or a medical record system — enables dynamic phototherapy tailored to the patient’s individual needs at different stages of the phototherapy. In some embodiments, communication between the computing system 114 and the medical record system 116 may allow integration of the phototherapy data produced during a phototherapy session (e.g., realtime irradiance levels, exposure times, frequency of phototherapy and the like) with a therapy model for future use. In some cases, the computing system 114 may use a machine learning model trained using previous patient data and corresponding phototherapy data to control and adjust an irradiance of the therapy light 126 generated by the light source 101 and a duration of patient’s exposure to eth therapeutic light, or provide a suggested value of irradiance of the therapy light 126 and / or a suggested duration of the phototherapy. In various implementations, the system may integrate advanced machine learning techniques — such as predictive analytics, adaptive algorithms, and personalized recommendation engines — to deliver intelligent and responsive phototherapy. These approaches can enable features like real-time performance optimization, dynamic treatment adjustments, outcome prediction, and continuous learning from patient and phototherapy data, thereby ensuring a more effective and tailored therapeutic experience.

[0092] In some embodiments, the computing system 114 (or the controller 104) may comprise a non-transitory memory storing machine readable instructions and a processor configured to execute the machine-readable instructions to monitor and control real timeirradiance of the therapeutic light 126 at the target surface. Additionally, the processor may receive patient data (e.g., regularly, periodically, randomly, or as needed), determine a target irradiance based on the patient data, and control the light source 101 deliver the target irradiance to the patient 124. In some embodiments, the computing system 114 (or the controller 104) may comprise a graphical user interface (GUI) configured to graphically present temporal variation of one or more parameters associated with the phototherapy to the operator 120 and / or a physician. For example, bilirubin trend over time may be displayed in the GUI to enable timely clinical decision-making informed by real time monitoring.

[0093] In some embodiments, the computing system 114 (or the controller 104) may be configured to allow secure data logging for clinical validation and longitudinal epidemiological research.

[0094] In some cases, transcutaneous and serum bilirubin values (TcB and TsB) of a patient may be measured based on a treatment plan and / or a timetable generated by the computing system 114 and provided to the computing system 114 by the medical record system 1116 and / or via a secure data login interface of the computing system 114. In some cases, transcutaneous bilirubin (TcB) may be measured using a non-invasive handheld device that estimates bilirubin levels through patient’s skin. In cases, the handheld device may use multiwavelength optical spectroscopy to measure TcB. For example, the handheld device may emit light of different wavelengths onto the skin (usually the forehead or sternum) and measure the intensity of reflected light to calculate bilirubin concentration based on absorption patterns associated with absorption of specific wavelengths absorbed by the bilirubin in subcutaneous tissue.

[0095] This infrastructure supports longitudinal research on treatment efficacy, bilirubin kinetics, and safety. It lays the groundwork for multicenter clinical trials and future development of personalized phototherapy protocols.

[0096] FIG. 2A illustrates an example phototherapy system 200 configured to provide therapeutic light to a patient 124 in accordance with certain embodiments of the present disclosure. The phototherapy system 200 may comprise one or more features described above with respect to the phototherapy system 100. In some embodiments, the phototherapy system 200 may comprise a light source that is integrated with a control and supply unit 102 within a common housing or enclosure 201. In some cases, the light source of the phototherapysystem 200 can be a light box 210 configured to illuminate the treatment area of a patient 124 (or a target surface region) with diffuse and uniform irradiance. In some cases, the light box 210 may comprise an arrangement of illumination units and reflecting optical surfaces configured to generate therapeutic light 126 having diffuse and uniform irradiance. In some embodiments, the light box 210 may comprise at least one light emitting unit (e.g., one or more light emitting elements such as light emitting diodes) and at least one optical reflector or optically reflective surface configured to reflect and redirect at least a portion of light received from the light emitting unit toward the target surface region. In some embodiments, the light box 210 may comprise an illumination unit comprising at least one light emitting element and at least one reflector. In some examples, the light emitting element can be a light emitting diode (LED) and the light emitting unit can be an array of LEDs. In some cases, the light box 210 may comprise an array (e.g., two-dimensional array) of illumination units arranged in a matrix. In the example shown, the light box 210 includes two illumination units each comprising a reflector 208 and a light emitting unit 202 (e.g., an LED array). In some examples, the reflector 208 can be a parabolic reflector and the light emitting unit 202 may be positioned at the focal point of the parabolic reflector. However, the embodiments are not so limited and the light box 210 may comprise other arrangements of light emitting units or elements and optically reflective surfaces. For example, the optically reflective surface of at least one illumination unit may form an optically integrating shell configured to integrate light emitted from an illumination unit or element. In some embodiments, the light box 210 may comprise an output window 211 configured to reflect at least a portion of the light received from each illumination unit and / or make the therapeutic light 126 more diffused and uniformly distributed over the treatment area. In some cases, the combination of reflector 208 and output window 211 can substantially improve the uniformity of therapeutic light 126, resulting in a more even spatial distribution of irradiance across the treatment area compared to a light source lacking one or both reflector(s) and output window 211.

[0097] In some embodiments, the microcontroller 204 may use pulse width modulation (PWM) to control the output optical power (e.g., average output optical power) of the light box 210. In some such embodiments, the microcontroller 204 may generate a pulse width modulated driver signal (e.g., a current or voltage) and transmit the driver signal to the driver 106 to drive the light box 210. By controlling the duty cycle or pulse widths of the driversignal, the microcontroller 204 may adjust the optical power (e.g., average output optical power) of the therapeutic light 126 generated by the light box 210.

[0098] In some embodiments, the phototherapy system 200 may comprise a display and control panel 206 configured to display various parameters controlled and / or read out by the microcontroller 204. In some cases, the display and control panel 206 may comprise a touch-screen display configured to receive user inputs. In some examples, the display and control panel 206 may display an irradiance detected by a photonic dosimeter probe 122a. In the example shown, the microcontroller 204 may receive a sensor signal indicative of an irradiance detected by the photonic dosimeter probe 122a, from the photonic dosimeter circuit 122b. In some embodiments, an electronic readout circuit may be integrated with the photonic dosimeter probe 122a to form a radiometer probe and the microcontroller 204 may receive a sensor signal from the photonic dosimeter probe 122a. In some cases, the electronic readout circuit may comprise an averaging circuit. In some embodiments, the microcontroller 204 may receive a sensor signal from the photonic dosimeter circuit 122b which receives a raw sensor signal from the photonic dosimeter probe 122a and generates the sensor signal (e.g., by at least averaging the raw sensor signal received from the photonic dosimeter probe 122a).

[0099] In some cases, the microcontroller 204 can be programmed to adjust the duty cycle of the driver signal to modulate a current provided to the LEDs to give calibrated irradiance which is displayed on the display and control panel 206. In some embodiments, one or both the photonic dosimeter sensor (or probe) 122a and photonic dosimeter circuit 122b may be detached when phototherapy system 200 is in operation (e.g., provides phototherapy to the patient 124). In some such embodiments, the photonic dosimeter circuit 122b and / or the photonic dosimeter probe 122a may be used to calibrate the irradiance displayed on the display and control panel 206 (or on the computing system 114) based on the measured irradiance of the therapeutic light 126 according to a sensor signal generated by the photonic dosimeter circuit 122b and / or photonic dosimeter probe 122a.

[0100] In some cases, the microcontroller 204 may comprise advanced functionalities, including adjustable irradiance levels, real-time dose display, self-calibration, and the ability to download patient metrics and treatment plans for epidemiological studies. In some cases, the microcontroller 204 may be configured to communicate with the computing system 114 (e.g., a laptop or a tablet), via a wired or wireless link, to enable seamless operationvia the computing system 114 to ensure a standardized, efficient, and user-friendly approach to delivering consistent and effective phototherapy (e.g., a to a neonatal patient). In some cases, one or both the photonic dosimeter circuit 122b and photonic dosimeter probe 122a can be detached from the phototherapy system 200 and tested independently for calibration during specified intervals, such as monthly, semiannually, annually, or as otherwise required.

[0101] In some embodiments, the photonic dosimeter circuit 122b and radiometer probe 122a may be configured to provide a feedback signal to the microcontroller 204 during a phototherapy session to maintain the irradiance of the therapeutic light 126 at a specified value displayed on the display and control panel 206. In some cases, the specified value may be provided by a user via the display and control panel 206 or the computing system 114. ‘

[0102] In some embodiments, the light box 210 may include a cooling system 209 configured to remove heat generated by the light emitting units of the light box 210. In some cases, the cooling system 209 may be powered by the power supply 108. In some examples, the cooling system 209 may be controlled to maintain temperatures inside the light box 210 below a specified value.

[0103] As described above, some of the existing phototherapy systems may not deliver therapeutic light having spatially uniform irradiance over the therapy areas. For example, in some cases, existing phototherapy systems may employ intense point-source LEDs directed at an infant, often resulting in non-uniform irradiance and localized hotspots that may pose safety risks. Further, the irradiance therapeutic light provided by the existing phototherapy systems may not match or be close to an intended irradiance and / or an irradiance measured by a non-photonic dosimeter (e.g., due to difference between the spectrum of the therapeutic light and the spectral response of the radiometer).

[0104] In contrast, the phototherapy system 100 and its example implementation as the phototherapy system 200, herein referred to as standardized phototherapy system, may generate therapeutic light 126 having an irradiance uniformly or near uniformly distributed over a therapy area or region of the patient 124 (or the target surface 127). Moreover, irradiance of the therapeutic light 126 at the target surface 127 can substantially equal to a value displayed on the user interface 112 (e.g., the display and control panel 206) or a user interface of the computing system 114. In some embodiments, the spatially uniform distribution of irradiation may be associated with the optical design and configuration of the light box 210 furtherdescribed below with respect to FIGS. 3A-3D, 4A-4B, 5A-5C, 6A-6B, and the electronic configuration and design of the controller 104 and the driver 106. For example, an arrangement of plurality of light emitting units, optically reflecting surfaces, an exit window of the light box 210 may result in spatially uniform distribution of irradiation over the target surface 127. In some examples, an individual illumination unit of the light box 210 may be configured to generate light having a uniform spatial distribution over a specified portion of the target surface 217 illuminated by the individual illumination unit. In some examples, the controller 104 and the driver 106 may be configured (e.g., programmed during a testing / calibration process) to individually control the drive currents provided to the individual ones of the illumination units of the light box 210 to provide a spatially uniform distribution of irradiance over the a specified region of the target surface 217 illuminated by the light box 210.

[0105] In some embodiments, the accuracy of the irradiance value displayed on the user interface 112 or a user interface of the computing system 114 may be associated with the design and structure of the photonic dosimeter probe 122a, the design of a readout circuit, e.g., the photonic dosimeter circuit 122b or integrated with the controller 104, further described below with respect to FIGS. 10A-10E. In some cases, the photonic dosimeter 122 may comprise an optical sensor having a narrow-band responsivity whose peak responsivity lies within the full-width-half-max (FWHM) of the spectrum of the therapeutic light 126 (e.g., the FWHM of an LED used in the light emitting units of the light source 101 or light box 210). In some examples, the optical sensor of the photonic dosimeter 122 (e.g., the optical sensor of the dedicated optical probe 122a) can be a photodiode comprising the same material and, in some cases, the same PN junction as an LED used as the emitting element the light source 101 or light box 210. In some examples, the optical sensor of the photonic dosimeter 122 (e.g., the optical sensor of the dedicated optical probe 122a) can be an LED substantially identical to an LED used as the emitting element the of light source 101 or light box 210 but configured to detect light. In some cases, one or both the peak emission wavelength (e.g. a center wavelength) and the bandwidth of the LED used as optical sensor can be identical or substantially identical to those of an LED used in the light source 101 to generate therapeutic light. For example, in some cases, a peak emission wavelength of the LED used a optical sensor can be within ± 1%, within ± 2%, within ± 4%, within ± 5%. within ± 7%, of a peak emission wavelength of the at least one LED and a bandwidth of light emitted by the LEDused as the emitting element the of light source 101 can be within ± 1 %, within ± 2%, within ± 4%, within ± 5%, within ± 7%, of a bandwidth of light emitted by the at least one LED.

[0106] In some embodiments, the microcontroller 204, the driver 106 and the light box 210 may form a photon-pulse module. In some cases, where the light emitting units and elements of the light box 210 are LEDs, photon-pulse module may be referred to as photonpulse LED module. In some embodiments, a photon-pulse LED module may emit discrete quantum photonic pulses. In some examples, a photonic dosimeter and / or radiometer probe may be used to convert each pulse into an electrical signal, establishing a calibrated reference for spectral-irradiance measurement and dose tracking. In some cases, the driver 106 that receives driver signals (e.g., PWM signals) from the controller 104 (e.g., microcontroller 204) can be a custom designed driver configured generate a modulated current (or voltage) having a duty cycle and amplitude associated with the driver signal.

[0107] In some cases, the photon-pulse module can be a closed-loop controlled photon-pulse module configured to generate and control the therapeutic light 126 based on a sensor signal received from the photonic dosimeter 122 (e.g., photonic dosimeter circuit 122b and photonic dosimeter probe 122a). In some such cases, closed-loop controlled photon-pulse can be a closed-loop controlled photon-pulse LED module. In some cases, the photonic dosimeter 122 may integrate pulse counts (e.g., optical pulse counts of therapeutic light 126) received from the light source 10 and compute a delivered photonic dose based on the integrated pulse counts. The controller 104 of the photon-pulse LED module may receive a sensor signal indicative of, or comprising, the computed photonic dose from the photonic dosimeter 122, as a feedback signal. The controller 104 and use the sensor signal to adjust a duty cycle of the driver signal (e.g., the PWM duty cycle) in real time to ensure the therapeutic light 126 maintains a target irradiance at the target surface 127.

[0108] In some cases, the microcontroller 204 or the computing system 114 may comprise a control algorithm configured to adjust the irradiance at the target surface 127 based on TcB and / or TsB inputs received from an operator 120 or a medical record system 116.

[0109] In some embodiments, a hardware-in-the-loop simulation may be conducted using the phototherapy system 100 (or 200) and, in some cases, the computing system 114 to evaluate the stability and response time of the phototherapy system based on synthetic bilirubin trajectories provided to the system.

[0110] In some embodiments, the performance of the phototherapy system 100 (or 200) may be extensively examined during a testing period, to refine the parameters of the controller 104 and ensure that phototherapy system can deliver the desired therapeutic light and operate within a set safety limit. In some cases, the extensively examination may comprise iterative bench testing where the irradiance of therapeutic light is measured in response to various inputs provided by a user or a treatment algorithm.

[0111] In some embodiments, the phototherapy system 200 (or an alternative implementation of phototherapy system 100) may be mounted on a rolling stand, enabling it to be moved to different locations where phototherapy needs to be administered to a patient. FIG. 2B illustrates an example of a mobile phototherapy system 220, which includes the phototherapy system 200 mounted on a rolling stand 223 for bedside phototherapy treatment. In some embodiments, the rolling stand 223 may include a wheeled base and a mounting rod or bar 222. In certain cases, the height of the mounting rod may be adjustable — either manually or electrically — to vary the vertical distance (h) between the target surface 127 and the exit aperture of the phototherapy system 200. In some embodiments, the phototherapy system 200 may communicate with a mobile computing device 232 or a nearby computing device 230 via a wired link 235 or a wireless link 234.Light box structure and design

[0112] FIG. 3 illustrates cross-sectional bottom (bottom panel) and side (top panel) views of a light box 210 that may be used as the light source 101 of the phototherapy system 100 to generate therapeutic light 216. In some embodiments, the light box 210 may be configured This design ensures the production of indirect, diffuse light, enabling uniform irradiance across the treatment area and facilitating accurate measurement of light delivery.

[0113] In some cases, the light box 210 may comprising a plurality of illumination units arranged in an MxN array matrix (in the example shown M=2 and N=4). In some embodiments, and individual illumination unit 300 of the plurality of individual illumination units may comprise a light emitting unit 302 configured to emit light within a therapeutic bandwidth and an optical reflector 308 configured to reflect at least a portion of the light emitted by the light emitting unit 302 toward an exit aperture of the illumination unit 300, which faces the target surface 127. In some embodiments, the light emitting unit 302 maycomprise a plurality of the light emitting elements arranged in an array (e.g., a one-dimensional array). In some examples, number of light emitting elements in a light emitting unit can be from 2 to 6, from 6 to 8, from 8 to 10, from 10 to 20, from 20 to 100. or larger numbers. In some cases, the reflector 308 may comprise a specular, white-coated internal surface (facing the light emitting unit 302) having parabolic, spherical, ellipsoidal, semi-spherical, or other shapes configured to reflect light emitted by the light emitting unit 302. In some cases, the internal surface of the reflector 308 may comprise a surface having Lambertian or Lambertian- Like behavior to generate a uniform and diffuse reflected light. In some cases, the Lambertian or Lambertian-Like behavior may be provided by a coating formed on a substrate. In some embodiments, the individual illumination unit 300 may be configured to produce indirect, diffuse light, enabling uniform irradiance within a specified region of the target surface 127 illuminated by the illumination unit 300. In some embodiments, the plurality of the illumination units may be configured to the produce of indirect, diffuse light, enabling uniform irradiance within a specified region of the target surface 127 illuminated by the light box 210.

[0114] In some embodiments, the light box 210 may include an output window 211 extending laterally (e.g., in the xy-plane). In certain cases, the output window 211 may be configured to transmit a specified portion of light received from the plurality of the plurality of the illumination units while reflecting the remaining portion back toward the reflectors. Multiple reflections between the reflectors and the output window 211 may contribute to achieve a spatially uniform distribution of therapeutic light 126 across the exit aperture of the light box 210. In some examples, the output window 211 may be configured to transmit 45% to 55%. 55% to 65%, 65% to 75% of light incident on the output window 211, when light has wavelength within an operation wavelength of the light box 210. In some cases, the operational wavelength of the light box may comprise a therapeutic bandwidth (e.g., a therapeutic bandwidth associated with bilirubin phototherapy).

[0115] In some embodiments, the light emitting unit 302 may be positioned and oriented with respect to the reflector 308 such its emission primarily propagates above the light emitting unit 302 toward the reflector 308, and the reflector 308 may be configured to reflect light received to from the light emitting unit 302 to form a light beam propagating toward the output window 211 which may serve as the exit aperture of the light box 210. In some cases, a light beam exiting an individual illumination unit 300 can be collimated or near collimatedalong vertical direction (along z-axis). In some cases, the reflector 308 may include a specular, white-coated reflective surface formed by applying a coating layer of a specified shape. In certain embodiments, the layer may consist of an aluminum sheet shaped as required and coated with a reflective material that provides a specified reflectivity (e.g., greater than 95%) for light within the operational wavelength range of the light box 210.

[0116] FIG. 3B illustrates orthogonal cross-sectional views of an individual illumination unit 300 of the light box 210 shown in FIG. 3A depicting transverse (xz), longitudinal (yz) and horizontal (xy) cross-sections of the illumination unit 300. In the example shown, the reflector 308 may comprise a parabolic reflecting surface extending along x-axis and having a parabolic shape in the yz-plane. The light emitting unit 302 (e.g., a onedimensional array of LEDs) may be placed at the focal point of parabolic reflecting surface along x-axis.

[0117] In some cases, the individual illumination unit 300 may have a rectangular or square shape cross-section in a plane parallel to the exit aperture of the light box 210 (e.g., in xy-plane). In some examples, the cross-section of an individual illumination unit 300 in the x-y plane and at the exit aperture can be rectangular or square- shaped. In some examples, the cases, square cross-section can be approximately 10 cm x 10 cm, 15 cm x 15 cm, 20 cm x 20 cm or large or smaller values. In some examples, the width and length of the rectangular crosssection can be from 10 cm to 15 cm, from 15 cm to 20 cm, from 20 cm to 30 cm, or any ranges formed by these values or larger or smaller values.

[0118] In some embodiments, the parabolic reflector 308 may comprise an aluminum reflector coated with white and high diffuse reflective film (or coating) having a diffuse reflectivity greater than or equal to 90%, 93%, 95%, 97%, or 99% for light having wavelengths within the operational wavelength range of the light box 210.

[0119] In some embodiments, the light box 210 may comprise an enclosure 310 configured to house the plurality of illumination units.

[0120] FIG. 3C illustrates the measured angular luminous intensity distribution for an example light emitting unit 302, or a light emitting element 306 used to formed the light emitting unit 302 shown in FIG. 3B. FIG. 3C shows that a major portion of the optical power emitted by the light emitting unit 302 (or the light emitting element 306) is distributed within an angle centered along the z-axis. In some embodiments, an angular width of the reflector 308(e.g., the parabolic reflector 308) may be designed based on the angular luminous intensity distribution of the light emitting unit 302, or a light emitting element 306 used, e.g., angular luminous intensity distribution shown in FIG. 3C.

[0121] FIG. 3D illustrates transverse cross-sectional view of an example parabolic optical reflector 308 configured to capture and reflect light emitted from a light emitting unit 302 (or element 306) having an emission according to the angular luminous intensity distribution shown to FIG. 3C. In some embodiments, shape and one or both the width (w) of the reflector 308 along x-axiz and the height (Z) of the reflector 308 along z-axis may be determined based on the angular luminous intensity distribution of the corresponding a light emitting unit or element. In this example, the reflector 308 is configured to capture an angular portion of the distribution shown in FIG. 3C corresponding to relative luminous intensity greater than 20% (approximately ±75 degrees with respect to a direction normal to the reflector surface and passing through the focal point of the reflector). In some cases, a shape of the reflector 308 in the zx-plane may be determined based on an angular luminous intensity distribution of the corresponding a light emitting unit or element and the light emitting unit (or element) may be positioned at geometrically significant point (e.g., focal point) of such shape (e.g., a parabola).

[0122] FIG. 4A illustrates cross-sectional bottom (bottom panel) and side (top panel) views of another light box 410 comprising a plurality of illumination units. In some embodiments, the light box 410 and the illuminating units therein may comprise one or more features described above with respect to the light box 210 and its illumination units. In this example, an individual illumination unit 400 may comprise a reflector 408 (e.g., a hemispherical reflector) configured to form a closed volume with the output window 211, where the internal surface of the closed volume is configured to function similar to an integrating sphere and transform light emitting by a light emitting unit or element 406 to a diffuse light beam exiting the illumination unit via a corresponding region of the output window 211. FIG. 4B illustrates orthogonal cross-sectional views of an individual illumination unit 400 of the light box 410 shown in FIG. 4A depicting transverse (xz), longitudinal (yz) and horizontal (xy) cross-sections of the illumination unit 400. In some embodiments, a light emitting element 406 (e.g., an LED) may be positioned near a top portion of the reflector 408. In some cases, the light emitting element 406 of the illumination unit 400 may be placed in aport tube 405 and oriented such that light emitted by the light emitting element cannot reach the output window 211 without being reflected by the internal reflecting surface 401 o the reflector 408. In some examples, the port tube 405 may be extended substantially parallel to the output window 211. In some cases, the internal surface 407 of the reflector 408 may be coated with a reflective coating having a reflectivity greater than or equal to 90%, 93%, 95$, 97%, or 99% for light having wavelengths within the operational wavelength range of the light box 410. FIG. 4C illustrates three-dimensional views of the illumination unit 400 shown in FIG. 4B, as well as a light box 420 comprising 32 substantially identical illumination units of the type shown in FIG. 4B, arranged in a 4-by-8 matrix. In this example, the illumination units are grouped in sets of four 412, and eight such groups are combined to form the light box 420. In some cases, each group may be driven by a separate driver. In some cases, each group 412 may be placed in separate compartment 414 of the light box 420. In some cases, a light box may be formed by a larger or smaller number of illumination units, smaller or larger number of groups of illumination units, and each group may have a larger or smaller number of illumination units. In some cases, smaller illumination units (e.g., similar to illumination unit 400) may have a smaller height (along z-axis). As such light boxes formed by a larger number of smaller illumination units can have smaller thickness along a direction normal to the output window 211 (along z-axis).

[0123] Integrating spheres are benchmark devices for producing highly uniform optical output. They typically consist of hollow spherical cavities coated with Lambertian diffuse-reflecting materials that scatter incident light uniformly in all directions. This geometry eliminates hotspots and directional bias, enabling uniform irradiance at the exit port and over a defined surface at a given distance. Although integrating spheres are widely recognized as the gold standard for radiometric calibration, their use has not been practically implemented in phototherapy device design. Advantageously, the reflector 408 together with the output window 211 may function in an integrating sphere-inspired manner, generating diffuse, uniform optical output that produces uniform irradiance across the treatment region. This uniform distribution enhances neonatal safety and enables accurate and reproducible irradiance measurements. In certain embodiments, the reflector 408 may be configured as an integrating sphere-inspired hemispherical cavity transitioning to a square exit port, with the interior surface coated or laminated with a Lambertian-like high-diffuse reflective material. Such anintegrating sphere-inspired hemispherical-to-square geometry can improve uniformity while maintaining compact form factors suitable for modular illumination units.

[0124] In various implementations, a light box may be configured by arranging illumination units (e.g., illumination unit 300 or 400) in geometries different from those illustrated in FIGS. 3A, 4A, and 4C. In certain embodiments, the illumination units of the light box may be positioned to illuminate a target region that conforms more closely to the body shape of a neonate. FIG. 4D illustrates an example of such arrangement where a light box 420 is formed by six groups of illumination units of the type shown in FIG. 4B (illumination unit 400), where each group includes four illumination units placed in an individual compartment 414. FIG. 4B can be a bottom cross-sectional view of such light box 420 in a plane parallel to the exit aperture of the light box. In this example four groups (compartments) are arranged in two-by-two matrix at the center and two groups (compartments) are positioned at each longitudinal end of the lightbox. Note that an output window (not shown) may cover the output apertures of the illumination units (similar to the output window 211). In some examples, the output window may have the same shape as the light box 420. In some embodiments, one or more of the illumination unit groups in FIG. 4D may be replaced with one or more illumination units of the type shown in FIG. 3B (illumination unit 300). For example, the light box shown in 4D may include six illumination units similar to the illumination unit 300. As another example, the light box shown in 4D may include one or more illumination unit similar to the illumination unit 300 and one or more illumination units similar to the illumination unit 400.

[0125] FIG. 5A illustrates a three-dimensional schematic diagram of light box support frame 502, shown from a top perspective. In some embodiments, the light box support frame 502 may comprise a plurality of frame sections or housing compartments each configured to house an individual illumination unit (e.g., illumination unit 300 or 400) to form a light box (a therapeutic light source). In some embodiments, the light box support frame 502 may comprise a plurality of cooling units 504 mounted thereon and configured to provide an airflow to the light emitting units of the illumination units. In some cases, each cooling unit may be configured to provide airflow (e.g., laminar or near laminar air flow) across a column of the two-dimensional array illumination units. In the example, shown the light box support frame is designed to form a two-dimensional array of illumination units having two rows andfour columns (housing a total of eight illumination units) and comprises four colling units 504 each providing air flow to two illumination units in the same column.

[0126] FIG. 5B illustrates a three-dimensional schematic diagram of the light source support frame in FIG. 5A, shown from a bottom perspective depicting the parabolic reflectors 308. In some embodiments, neighboring illumination units within each row may be separated by a reflector support frame 508, which is configured to anchor the reflectors of adjacent illumination units to the light box reflector support frame 502. In certain cases, the support frame 508 may be designed to maintain a specified reflector shape. For example, to support a parabolic reflector, the reflector support frame 508 may include a parabolic edge to which the reflector is secured. In some cases, each reflector support frame 508 may comprise two supporting layers each supporting the reflector of one of the two neighboring illumination units (in a row). The close-up view in FIG. 5B illustrates one of the layers 508a- 1 of a reflector support frame 508a.

[0127] In some cases, the light box support frame 502 may include an airflow guide 506 placed over the colling units 504 and configured to assist with formation of a laminar or near laminar airflow across the light box support frame 502.

[0128] FIG. 5C illustrates an exploded view of a phototherapy system (e.g., phototherapy system 200) comprising the light box 210 (formed by the source support frame 502), depicting peripheral components (electronic modules and circuits) and certain functional accessories of the phototherapy system. In some cases, the power supply 108, microcontroller, touchscreen display 206, control panel, and driver 106 may be positioned above the light box 210 and light box support frame 502. The inset shows a close-up view of a reflector support frame 508a of the light source support frame 502. The reflector support frame 508a may comprise a first layer 508a-l, an intermediate layer 508a-3 and a second layer 508a-2, where the intermediate layer 508a-3 is configured to mechanically connect the first and second layers 508a-l, 508a-2. In some cases, the layers of the frame 508a may comprise plastic layers. In some embodiments, each of the first and second layers may comprise a curved (e.g., parabolic) edge 510 configured to support supporting the reflector of one of the two neighboring illumination units. In some cases, two emitter holders 509a- 1 and 509a-2 may be connected to the first and second layers 508a- 1. 508a-2, respectively, each configured to support the light emitting unit of one of the two neighboring illumination units. In some cases, each of the twoemitter holders 509a- 1 and 509a-2 may comprise a metal printed circuit board (PCB) with surface mount sockets for supplying electric current supply to the light emitting units.

[0129] FIG.6A is a schematic diagram illustrating a top view (top panel) of a lightemitting unit 601a comprising a one-dimensional array of light emitting elements 306 (eight LEDs in this example) a, circuit diagram 601b the light-emitting unit 601a and circuit diagram 603 of another light-emitting unit. In some cases, the spacing between neighboring LEDs in a one-dimensional array can be from 0.5 to 0.75 inches, from 0.75 inches to 1 inch, from 1 inch to 1.25 inches, from 1.25 inches to 1.5 inches, and any ranges formed by these values or larger or smaller values. In some examples, such as the light-emitting unit 601a / 601b, two LEDs may be electrically connected in parallel to form a LED. In some examples, such as the lightemitting unit represented by the circuit diagram 603, all the LEDs (e.g.. 6, 7, 8, ... LEDs) may be electrically connected in series.

[0130] FIG. 6B illustrates a three-dimensional schematic diagram showing the light-emitting unit 302 of FIG. 6A and a heat sink 604 (e.g.. aluminum heat sink). In some embodiments, the LEDs of the light emitting unit 302 may be mounted on a PCB 304. (e.g., an FR4 PCB). The light-emitting unit 302 may further comprise a heat sink configured to be connected to the PCB 304 by one or more screws 602.

[0131] In some embodiments, the uniformity of light emitted by an illumination unit of the light box 210 may be measured and verified by mapping irradiance of therapeutic light 126 using a 5 x 5 grid at a specified distance (e.g., 30 cm) from the exit aperture of the light source 101 or light box 210. In some cases, when the spatial variation of irradiance of the light emitted by the illumination unit at the specified distance does not exceed ±10% of a target value, the illumination unit may be used as one of the illumination units of the light box 210. In some embodiments, the light box 210 may be assembled using a plurality of illumination units that satisfy a spatial uniformity criteria (e.g., having spatial irradiance variation less than a threshold value at a specified distance) in a two-dimensional MxN array or matrix (e.g., a 2x4 matrix).Light source calibration

[0132] In some cases, after the light box 210 or 410 is assembled, the irradiance of the therapeutic light 126 generated by the light box 210 (or 410), at a specified vertical distancefrom the exit aperture of the light box 210, may be tested for the entire light box (all illuminating units of the light box). In some cases, the phototherapy system 200 may include built-in analog-to-digital converter (ADC) channels to receive the output of a radiometer (e.g., the photonic dosimeter 122) during the test, as the radiometer (or radiometer probe) is moved to different lateral positions (e.g., under each of the illumination units) within a test plane substantially parallel to the exit aperture of the light box 210 and positioned at the specified vertical distance from the exit aperture of the light box 210. In some cases, the irradiance of each illumination unit (e.g., irradiance at a specified distance from the exit aperture) may be measured both by the radiometer and standardized and calibrated optical spectrometer. In some cases, a peak value of the irradiance across the detected emission spectrum and / or a total irradiance obtained by integrating irradiance over the entire emission spectrum may be measured and recorded. In some cases, the sensor signal generated by the radiometer may be associated with the peak value or the total irradiance.

[0133] In some embodiments, individual built-in analog-to-digital converter (ADC) channels may control the electric power delivered to the individual illumination units of the light box 210. In some such embodiment, during the test each channel may auto-trim a drive current provided to an individual illumination such that the irradiance at the test plane does not vary more than ±5% over a target area on the test plane. In some cases, the target area can be vertical projection of the exit aperture on the test plane.

[0134] In some cases, during a calibration process, irradiance (e.g., spectral or total irradiance) of the therapeutic light generated by individual illumination units of the light box and / or the entire light box may be measured. The irradiance measurements (e.g., received from the photonic dosimeter 122 or an optical spectrum analyzer) may be transferred to and stored in a computing system (e.g., computing system 114). In some embodiments, the irradiance measurements for individual illumination units of the light box may be loaded into the controller 104 (e.g., directly or from the computing system) to generate calibration data (e.g., a lookup table). In some cases, the calibration data may be used to convert a driver signal (e.g., duty cycle and amplitude of a driver signal) to a measured irradiance. In some cases, the calibration data may be used to convert an irradiance sensor signal generated by the photonic dosimeter to a measured irradiance. In some cases, a row or column of the lookup table may include the peak and / or total irradiance measured by a standardized optical spectrometer, thesensor signals generated by the photonic dosimeter and one or more characteristics of the driver signal (e.g., duty cycle, amplitude, and the like) at the time of measurement. In some cases, the calibration process may be repeated for multiple distances from the exit aperture of the light box, to generate calibration data associated with each vertical distance. As such, in some cases, the calibration data may relate the duty cycle of the driver signal and the distance, which the radiometer probe and / or a probe of the optical spectrometer were positioned during calibration, to a measured value of total irradiance, peak irradiance, spectral irradiance, and / or of the irradiance signal.

[0135] In some embodiments, the controller 104 may use the calibration data associated with individual illumination units of the light box to drive the individual illumination units of the light box 210 such that irradiance therapeutic light generated by the individual illumination units at the specified target surface (e.g., target surface 127) are substantially equal to a peak or total irradiance provided by a user via a user interface or determined by an a phototherapy algorithm based on patient data (e.g., bilirubin measurements obtained invasively or non-invasively).

[0136] In some cases, during a phototherapy period, a selected duty cycle of the driver signal and a corresponding irradiance (e.g., determine by the system based on the lookup table) may be displayed on the user interface 112 (e.g., the display and control panel 206) the phototherapy system 100 (e.g., the phototherapy system 200). In some cases, the displayed value may match the value measured by the standardized optical spectrometer within ± 0.2 pW / cm2, + 0.5 pW / cm2, ±1 pW / cm2, ± 1.5 pW / cm2, + 2 pW / cm2, + 5 pW / cm2, or other tolerances, across the full spectral range.

[0137] In some cases, in addition to a desired irradiance a user or operator may provide a distance (h) between the target surface 127 and the exit aperture of the light source 101 (light box 210) to the phototherapy system 100 via the user interface 112 or the computing system 114. In some such cases, the controller 104 may use the distance (h) and the desired irradiance provided by the operator 120 or the computing system 114 to generate the drive current based on a row or column of the lookup table containing the vertical distance (h) and the desired irradiance or a row or column containing the closest values to the vertical distance (h) and the desired irradiance.

[0138] In some embodiments, during the calibration procedure (e.g., for a illumination unit of the light box) the radiometer prob and the sensor of the standardized optical spectrometer (spectroradiometer) may be positioned side-by-side at a specified vertical distance (e.g., 30 cm) from the light source 101. In some cases, the radiometer probe and the sensor may be mounted facing directly the exit aperture of the light box. Subsequently the duty cycle of the driver signal (the pulse width modulated signal) may be increased step wise from 20% to 80% with a step size of 10 %. At each step, the value measured by the radiometer (e.g., display on display of the corresponding readout circuit) and the peak irradiance (e.g., at a peak therapeutic wavelength such 475 nm or 478 nm for bilirubin therapy) or integrated irradiances measured by the spectroradiometer may be recorded. In some cases, these measurements may be used to converts the radiometer’ s analog voltage into a digital value in pW / cm2. In some cases, the optical input may not be cosine-corrected, based one or more clinical reasoning including: 1) the skin may experience all incident photons, regardless of angle, 2) cosine correction may underestimate therapeutic dose from angled light, and 3) by omitting cosine correction, the radiometer may better reflect actual photonic energy received by neonatal skin.

[0139] FIG. 7A illustrates, measured intensity of light emitted by a therapeutic light source at a peak therapeutic wavelength as a function of the normal distance from the exit aperture of the therapeutic light source.

[0140] FIG. 7B illustrates a nine-point irradiance measurement configuration for measuring the uniformity of therapeutic light generated by a light box (e.g., light box 210 or 410) over a target region or area on a target surface. In some cases, the target surface can be a plane parallel to the exit aperture of the light box (e.g., parallel to the output window 211) and placed at a specified normal distance with respect to the exit aperture of the light box. In some cases, for given driver signal(s) provided to the driver(s) that drive the emission units the light box, the irradiance (e.g., peak spectral irradiance) may be measured using a photonic dosimeter, a radiometer, or a spectroradiometer at nodal points (i,j,), i and j=l,2,3, at formed by the cross-sections of the lines that divide a length (Lb) and a width (Wb) of the target region into nine identical rectangles. In some cases, the optical probe of a spectroradiometer may be placed at each nodal point to obtain nine irradiance values indicatives of spatial variation of irradiance generated by the corresponding light box over a given target region and for given driver signal. Table 2 below shows the peak values of spectral irradiance of an example lightbox (similar to light box 210) measured at nine nodal points (i,j) shown in FIG. 7B of a target region having a length of Lb = 60 centimeters and a width of Wb = 30 cm and at a normal distance of 30 cm from the exit aperture of the light box. These results show that for the light box under test the variation of peak spectral irradiance was less than or equal to 6% per centimeter (the rows correspond to the first index, i, and column correspond to the second index, j, of the nodal points (i , j) in FIG. 7B).Table 2

[0141] FIG. 7C illustrates, an example setup 700 for measuring the uniformity of irradiance generated by a therapeutic light source 704. In some embodiments, the spatial uniformity of therapeutic light generated by therapeutic light source 704 may be characterized by measuring irradiance (e.g., peak irradiance or total irradiance) through an irradiance measurement plate 710 positioned at a given distance Lc and parallel to the exit aperture or the output window 706 of the therapeutic light source 704.

[0142] In some cases, the therapeutic light source 704 may comprise a plurality of illumination units arranged in matrix. In the example shown the therapeutic light source 704 includes four illumination units of the type shown in FIG. 4A and 4B. As described above this type of illumination unit, herein referred to as integrating-sphere-inspired illumination unit, may be configured to generate uniform, diffuse optical field based on multiple reflection of light within a cavity having a reflective internal surface.

[0143] In some cases, an individual illumination unit 702 may comprise an LED 702a and a dome shaped reflector 702b having a square-shape exit aperture (3”x3” square in the example shown). The LEDs of the illumination units may be driven by a control and supply circuit 701. In some examples, the output window 706 of the therapeutic light source 704 may include a semi-reflective plate or diffuser (e.g., having a reflectivity of about 50% at the peak wavelength of the therapeutic light, e.g., at 475 nm) that can slide into a slot to cover the exitapertures of the corresponding illumination units. Tn some embodiments, the irradiance measurement plate 710 may comprise one or more measurement apertures. The irradiance measurement plate 710 may be positioned at specified normal distance Lc from the exit aperture of the therapeutic light source 704 (e.g., from the output window 706) and parallel to the exit aperture and the output window 706. The which light emitted by the therapeutic light source 704 may reach a radiometer probe (e.g., a photonic dosimeter probe), or a spectroradiometer probe. The radiometer probe or spectroradiometer probe may be placed closely behind an individual measurement aperture 709 to measure irradiance of a portion of light transmitted the measurement aperture 709. By moving the radiometer probe or spectroradiometer probe behind different measurement apertures of the irradiance measurement plate 710. an irradiance map or matrix may be generated. Such irradiance map or matrix may indicate a uniformity of the irradiance generated by the therapeutic light source 704 at a specific measurement distance Lc (e.g., 30 cm). In the example shown, the irradiance measurement plate 710 includes nine measurement apertures arranged in a 3 by 3 matrix. In other embodiments, measurement plates having smaller or larger number of measurement apertures arranged in different geometries may be used to characterize spatial uniformity of the light emitted by a therapeutic light source. In some cases, a measurement plate 708 having a single measurement aperture may be used to measure irradiance symmetrically around an axis passing through a center of the therapeutic light source 704, normal to the exit aperture of the measurement plate 710. In some cases, a measurement aperture can have a diameter from 0.5 inch to 1 inch, from 1 inch to 2 inches, from 2 inches to 3 inches, from 3 inches to 4 inches, or any range formed by these values or larger or smaller.

[0144] In various implementations, the internal or reflecting surface of any of the reflectors or integrating cavities described above may comprise a surface having Lambertian or Lambertian-Like behavior to generate a uniform and diffuse reflected light. In some cases, the Lambertian or Lambertian-Like behavior may be provided by a coating formed on a substrate.

[0145] FIG. 8 illustrates a circuit diagram depicting a portion of an electronic circuit used to drive and control a therapeutic light source (e.g., light box 210). In some cases, electronic circuit may comprise two or more drivers each configured to provide drive current to one or a group of illumination units. The characteristics of the drive current (e.g., amplitudeand / or duty cycle) provided by each driver may be controlled by the amplitude and duty cycle of driver signal provided by a microcontroller 204 to the driver. In the example shown, four drivers (e.g.. constant current drivers) 804-1, 804-2, 804-3, and 804-4 each provide drive current to a pair of illumination units of four pair of illumination units 806-1, 806-2, 806-3, and 806-4 of a light box. In some examples, the power supply 108 may provide electric power to each one of the four the drivers 804-1, 804-2, 804-3. and 804-4. In some cases, each pair of illumination units may comprise two light emitting units (e.g., two LED arrays or two LEDs) electrically connected in series to the corresponding driver. In some embodiments, the drive current provided by a driver to a corresponding pair of illumination units, thereby an irradiance generated by the pair of illumination units, may be controlled by a driver signal provided to the driver by the microcontroller 204. In some cases, the microcontroller 204 may provide individual and independently controlled driver signals to the drivers 804-1, 804-2, 804-3, and 804-4 via individual ones of four signal modification circuits (e.g., pulse squaring circuits) 802-1, 802-2, 802-3, and 802-4. In some cases, the signal modification circuits 802-1, 802-2, 802-3, and 802-4 may not be needed and the controller may directly transmit the driver signals to the drivers 804-1, 804-2, 804-3, and 804-4. Advantageously controlling individual drivers, and thereby irradiance of individual groups of illumination units, may allow adjusting irradiance generated by each illumination unit, e.g., during a calibration period, to improve the spatial uniformity of irradiance generated by the light box over a target region. In some embodiments the microcontroller 204 may provide one driver signal to two or more drivers. In some cases, each driver may provide driver current to a single illumination unit or more than two illumination units.

[0146] In some cases, the microcontroller 204 may allow a user to adjust a duty cycle of the driver signal and thereby the irradiance of the therapeutic light generated by the four pair of illumination units 806-1. 806-2. 806-3. and 806-4. via the user interface 206 (e.g., a touch screen display). In some cases, the user interface 206 may display a 0 to 100 % dutycycle progressive bar indicative of the duty cycle of the driver signals and as the user may moves the bar, the microcontroller 204 may update and display the corresponding irradiance in pW / cm2beside it (based on the look up table). In some cases, each driver signal may be linked to an actual irradiance reading in the lookup table stored in microcontroller 204, allowing direct digital readout of calibrated irradiance.

[0147] FIG. 9 A illustrates a measurement setup that may be used to characterize light emitted by a therapeutic light source with, e.g., respect to normal distance from the exit aperture of the therapeutic light source. In some cases, the measurement setup may comprise the photonic dosimeter probe 122a and a readout circuit comprising an averaging circuit 902 and an impedance matching circuit 904. The output of the photonic dosimeter probe 122a (e.g., a dedicated optical sensor) may be provided to the averaging circuit 902 and the output of the averaging circuit 902 may be provided to a measurement circuit 904 (e.g., an analog-to-digital converter) configured to display the measured value of the sensor signal generated by the photonic dosimeter probe 122a. In some one example, the photonic dosimeter probe 122a may be placed at a specified distance (e.g., 30 cm) from a therapeutic light source 101 (e.g., the light box 210). and the values displayed by the measurement circuit 904 may be recorded as the duty cycle of a driver signal provided to the light source 101 is changed. FIG. 9B illustrates the measured voltages measured by the measurement circuit 904 as the duty cycle of the driver signal provided to the light source 101 is increased in a step wise manner from 0 to 90% with a step size of 10%. FIG. 9B shows that the measured irradiance is substantially proportional to the duty cycle (linearly increases with the duty cycle) and therefore can be reliably controlled and adjusted by controlling the duty cycle of the driver signal provided ot the driver 106.Photonic dosimeter

[0148] Accurate irradiance measurement can be essential for effective phototherapy in particular neonatal phototherapy. Spectroradiometers (optical spectrum analyzers) can directly measure spectral irradiance (Es), in unit pW / cm2 / nm, based on fullwidth-half maximum of the emission spectrum (FWHMS) where Es = E -? FWHMS, whereas radiometers with optical filter yield a filtered spectral irradiance response (ER) based on fullwidth-half maximum of corresponding filer (FWHMR) where ER = E t-FWHMR. A narrowband LED source has FWHMS ~ 20 nm while a typical radiometer filter has FWHMR ~ 40 nm. Thus, the spectral irradiance ER measured by a filter-based radiometer can be inaccurate due to difference between the actual FWHM of the emission spectrum and the FWHM of the optical filter used. For example, when measuring light having a total irradiance of 600 pW / cm2the spectroradiometer the reports Es ~ 30 pW / cm2 / nm, whereas the filtered radiometer underreports: ER « 15 pW / cm2 / nm. Such discrepancies in irradiance measurementcan result in suboptimal treatment decisions in neonatal care, underscoring the critical need for standardization. As clinical studies reveal the advantage of narrowband bilirubin phototherapy using light within 476-478 nm, modern phototherapy systems may generate therapeutic light using narrowband LEDs having emission spectrums comprising a narrowband (FWHM ~20 nm) around a peak therapeutic wavelength (e.g., 475 nm, 476 nm, or 478 nm). Given the cost and complexity of producing narrow band optical filters having FWHMRs matching the FWHM of the emission spectrum of the narrow band LEDs, the mismatch between spectral response of currently available radiometers and the emission spectrum of the narrow band LEDs can result in inaccurate irradiance readings. The lack of narrowband-matched radiometers highlights the need for radiometers having optical sensors having inherently narrow spectral response. Such radiometers, having intrinsic narrow band response, may be used to accurately measure the spectral irradiance of therapeutic light generated by narrowband LEDs.

[0149] In some embodiments, a photonic dosimeter 122 (e.g., the dedicated radiometer of the phototherapy system 100) may comprise an optical sensor (e.g., an optical - to-electrical converter) that has spectral response matched, close to, or substantially identical to the emission spectrum of a therapeutic light source (e.g., light source 101). In some cases, a bandwidth (e.g., FWHM) of the spectral response of a photonic dosimeter is limited by the intrinsic response of the optical sensor (e.g., the response of a PN junction) without the need for an optical filter to eliminate out of band wavelength. As such, in some cases a photonic dosimeter of a phototherapy system can be a radiometer having an optical sensor spectrally matched to the therapeutic light source of the phototherapy system (e.g.. matched to the emission spectrum of the LEDs used in the therapeutic light source). In various implementations, the spectral response of a spectrally matched radiometer can have a FWHM from FWHM to 1.2xFWHM. from 1.2xFWHMS to 1.5xFWHM. from 1.5xFWHMS to 2xFWHM, from 2xFWHMS to 2.5xFWHM, from 2.5xFWHMS to 3xFWHMS, from 3xFWHMS to 3.5xFWHM, from 3.5xFWHMS to 4xFWHMS, or any ranges formed by these values or larger or smaller values, where FWHMS is the FWHM of the emission spectrum of the therapeutic light source to which the radiometer is spectrally matched.

[0150] In various implementations, the spectral response of a spectrally matched dedicated radiometer (the photonic dosimeter) can have a peak response can be substantiallymatched to the peak emission wavelength (Xc) of the therapeutic light source. For example, the peak response of the spectral response of a spectrally matched radiometer may lie within ±1%, ±2%, ±5% of Xc, or within any range formed by these values. In certain implementations, the radiometer peak wavelength may differ from Acby no more than ±1-3 nm.

[0151] In some embodiments, the radiometer’s spectral peak may be substantially matched to the peak emission wavelength (1c) of the therapeutic light source. These ranges are provided to encompass alternative embodiments while the preferred implementation uses an LED sensor whose peak wavelength substantially matches the source LED. LED supplies can be binned for 1c with ±1 nm. So, it would be safe to have at least 3 nm and matching photonic dosimeter will be also within that range 1-3 nm.

[0135] In some cases, the intrinsically narrowband spectral response of a spectrally matched radiometer can improve the accuracy of the spectral irradiance measurements without the need to filter the incident therapeutic light using an optical filter (e.g„ a narrowband optical filter). Thus, the spectrally matched radiometer (e.g., spectrally matched to a therapeutic light source) can provide a low-cost solution to the problem of discrepancy between the actual spectral irradiance and measured spectral irradiance of therapeutic light generated by therapeutic light source. Given that the total irradiance is determined by integrating the spectral irradiance over the emission spectrum of the therapeutic light source, a more accurate measurement of the spectral irradiance results is a more accurate measurement of the total irradiance. Note that the total irradiance (unit: pW / cm2) delivered to a target surface can be obtained by calculating:Total Irradiancewhere E^is the spectral irradiance in pW / cm2 / nm, where X? and i are the upper and lower bounds of the emission spectrum, respectively.

[0152] FIG. 10A illustrates spectral intensity (emission spectrum) of light emitted by a therapeutic light source (solid curve) and spectral responsivity of a typical radiometer (dashed curve) used to measure the spectral irradiance of the light. The photocurrent generated by the radiometer is proportional to a portion of the area under the emission spectrum and spectral responsivity (hashed region). Thus, the photocurrent can be smaller than the total irradiance. Moreover, since the radiometer reports a spectral irradiance based on the FWHMRof its response (instead of the FWHMS of the emission spectrum), the reported spectral irradiance is erroneous both due to error in the total irradiance measurement and the bandwidth.

[0153] FIG. 10B illustrates spectral intensity of light emitted by a therapeutic light source (solid curve) and spectral responsivity of an example dedicated photodetector (dotted curve) that is spectrally matched with the therapeutic light source. In the example shown in FIG. 10B, the spectral response of the radiometer is substantially equal to the spectral emission of the therapeutic light source (e.g., an LED with Xc~ 475 nm and FWHMS ~ 20 nm). Thus, in this case the spectral irradiance and total irradiance reported by the radiometer are both accurate and are both substantially equal to the actual spectral irradiance and total irradiance of the light source.

[0154] In some embodiments, the optical sensor of a photonic dosimeter spectrally matched to a therapeutic light source can be a photodiode or LED comprising the same material and the same semiconductor junction(s) (e.g., a PN junction) as an LED of the emitting element of the therapeutic light source. For optical example, the optical sensor of a photonic dosimeter can be an LED substantially identical to an LED used to generate the light detected or measured the photonic dosimeter. In some examples, the optical sensor of a radiometer spectrally matched to a therapeutic light source can be the substantial the same type of LED used as the emitting element of the therapeutic light source. In these examples, the LED may be used as an optical sensor in the radiometer and as a light emitting element in the therapeutic light source.

[0155] In some embodiments, the photonic dosimeter 122 photonic dosimeter probe 122a can include an optical sensor having a spectral response substantially matched or close to a spectrum of the therapeutic light 126 or an emission spectrum of the light box 210. In some embodiments, the readout circuit may be calibrated and / or designed based on the spectral response of the radiometer probe (e.g., the optical sensor therein) and emission spectrum of the light box 210.

[0156] In some cases, the photonic dosimeter 122 or photonic dosimeter probe 122a may comprise an optical sensor having a narrow-band responsivity whose peak responsivity lies within the full-width-half-max (FWHM) of the spectrum of the therapeutic light 126 (e.g.. the FWHM of an LED used in the light emitting units of the light source 101 or light box 210).

[0157] In some embodiments, a photodiode (e.g., an LED substantially the same as the light emitting element of the therapeutic light source 101), which is selected to serve as the optical sensor of the photonic dosimeter 122 (or the photonic dosimeter probe 122a) may be characterized using one or more illumination units of the light source 101. The characterization may comprise calibrating the sensor signal (e.g., photocurrent) generated by the optical sensor with the irradiance measured by a standardized spectroradiometer (or optical spectrum analyzer), when the optical sensor and the standardized spectroradiometer are illuminated by the same light source.

[0158] In some cases, the outcome of such characterization may be used to design a firmware or readout circuit of the photonic dosimeter 122 (e.g., the photonic dosimeter circuit 122b) to generate a sensor signal that is more accurate (closer to the actual irradiance or spectral irradiance).

[0159] Advantageously, a photonic dosimeter that is spectrally matched to the therapeutic light source, may not include a spectral filter or, in some cases, a conventional diffuser. Because LED phototherapy systems emit light within a narrow, well-defined spectral band, a single, spectrally matched photosensor can accurately detect the relevant photon flux. This eliminates unnecessary complexity and cost, enabling a simpler and more precise measurement system tailored to current-generation phototherapy devices.

[0160] The irradiance measurement process based on spectrally matched radiometer may comprise: receiving, by a spectrally matched optical sensor (e.g., an LED used as a detector), a photon flux (AQ) corresponding to a light pulse generated by one or more LEDs, converting AQ to a voltage AV proportional to AQ, using an electronic circuit (a readout circuit) averaging AV, providing the averaged AV to a microcontroller via a matching circuit, converting, by the microcontroller, the averaged AV into real-time action- spectrum- weighted spectral irradiance (unit: pW / cm2 / nm). peak spectral irradiance, or total irradiance (unit: pW / cm2).

[0161] Since LEDs are current-driven, each electrical pulse yields a proportional optical emission. When the LED drive current is modulated via pulse-width modulation (PWM), the total charge per pulse can be expressed as:

[0162] geiectricai = / pulse x Atpuise <x Quantum Photonic Pulse

[0163] Where geiectricai is the electrical charge delivered per pulse, 7pUise is the amplitude of the current pulse, and A / puia- is the duration of the pulse.

[0164] This charge drives the emission of a quantum photonic pulse, with radiant energy directly proportional to ^electrical. Given the constant quantum efficiency and spectral stability of LEDs, the resulting optical pulse energy is linearly proportional to the current pulse — and thus to the electrical charge.

[0165] These photonic pulses are projected onto the irradiance measurement plane and can be quantified by a spectrally calibrated radiometer or spectroradiometer. This implies that the electrical pulse characteristics are directly correlated with the spectral irradiance delivered, forming the basis for real-time dosimetry. It should be understood that such spectrally matched photon dosimetry is not the same as light intensity measurement performed by conventional radiometers that use diffusers and / or filters. Table 2 below summarizes some of the advantages of using a spectrally matched radiometer compared to a conventional radiometer:Table 2

[0166] In some cases, a conventional radiometer used to measure a non- homogeneous light source, may use cosine correction and a filter to measure an averaged flux density normal to a corresponding photosensor, e.g., to avoid hotspots. Given that human skin (e.g„ skin of a neonate) experiences hotspots, for measuring the irradiance of homogeneous therapeutic light incident on skin, the photonic dosimeter (spectrally matched radio meter) may not use cosine correction.

[0167] The photonic dosimeter may verify these emissions using a spectrally matched detector, closing the feedback loop to maintain both cumulative dose and spectral fidelity. This PWM-based photonic control strategy enables precise, patient-specific phototherapy. These improvements directly address clinical concerns regarding irradiance variability and safety, as identified in recent neonatal phototherapy research.

[0168] In some cases, the photonic dosimeter 122 of the phototherapy system 100 may comprise an optical sensor having a narrow-band responsivity whose peak responsivity lies within the full-width-half-max (FWHM) of the spectrum of the therapeutic light 126 (e.g., the FWHM of an LED used in the light emitting units of the light source 101 or light box 210). In some examples, the optical sensor of the photonic dosimeter 122 (e.g., the optical sensor of the dedicated optical probe 122a) may comprise the same material and the same PN junction as an LED used as the emitting element the light source 101 or light box 210. In some cases, a first doping concentration profile and first material composition of a first PN junction of the optical sensor, the PN junction that absorbs the therapeutic light, can be identical or substantially identical to a second doping concentration profile and second material composition of the second PN junction of the LED, the PN junction that emits the therapeutic light. In some examples, the optical sensor of the photonic dosimeter 122 can be an LED substantially identical to the light emitting element (e.g., LED) 306 of the light box 210 or 410. In some cases, the optical sensor of the photonic dosimeter 122 (e.g., the optical sensor of the dedicated optical probe 122a) may be selected by an optical sensor selection process comprising measuring the emission spectrum of a plurality of LEDs using a NIST-traceable spectroradiometer and selecting an LED whose emission spectrum matches the emission spectrum of the light source 101 or light box 210 (e.g., emission spectrum of an LED therein) with ± 5 % agreement across the emission band. In some embodiments, the plurality of LEDs may comprise the same material and the same PN junction as an LED used as the emitting element the light source 101 or light box 210. In some embodiments, the plurality of LEDs can be substantially identical to the LED used as the emitting element the light source 101 or light box 210.

[0169] FIG. 10C illustrates an example circuit for transforming photocurrent generated by a photodiode or an LED serving as a detector, upon being illuminated, to an input voltage usable by a control and / or measurement circuit. In some cases, the readout circuit maycomprise an averaging stage and a impedance matching stage as described above with respect to FIG. 9A.

[0170] FIGS. 10D-10E illustrate a schematic cross-sectional side view (10D) and a photograph (10E) of an example of spectrally matched radiometer and / or the dedicated radiometer. In some embodiments, the spectrally matched radiometer and / or the photonic dosimeter may comprise an optical sensor 1002 mounted on a circuit board 1006. In some cases, a dome-shaped cover 1004, may be placed on the optical sensor 1002 (e.g., an LED) to protect optical sensor 1002 from the dirt or other obstructions. In some examples, the domeshaped cover 1004 can have an optical transmission equal or greater than 90% for the wavelengths emitted by a therapeutic light source monitored or characterized by the spectrally matched radiometer (photonic dosimeter). The circuit board 1006 may comprise the readout circuit shown in FIG. 10C. In some cases, the optical sensor 1002 can be an LED of the same type or substantially identical to an LED used in a corresponding the therapeutic light source (e.g., the light emitting element 306)Irradiance Lab Standard (ILS)

[0171] In some cases, an irradiance lab standard (ILS) may be used to calibrate the dedicated radiometer (e.g., a spectrally matched radiometer) such as the photonic dosimeter 122. In some cases, the photonic dosimeter may serve as a transfer- standard radiometer that is a purpose-built and detachable dedicated radiometer serving as a traceable irradiance calibration reference. The transfer- standard radiometer can be detached from the phototherapy system to be calibrated against a NIST-traceable spectroradiometer. In some cases, the transfer- standard radiometer, e.g., the photonic dosimeter 122, may be connected to the phototherapy system 100 during a phototherapy session or during a regular testing session (e.g., every week or every month) to verify the accuracy of irradiance displayed on the user interface 112 of the phototherapy system 100 or a display of the computing system 114.

[0172] In some cases, the irradiance lab standard (ILS) may comprise a dedicated experimental setup comprising a light source configured to generate light with a high level of spatial uniformity. In some cases, the light source may comprise an integrating- sphere 1102 and an LED 1104 (e.g., of the same type used in the therapeutic light source), which delivers spatially uniform, narrow-band light with a peak or center wavelength and bandwidthsubstantially equal to those of the therapeutic light. Tn some cases, the LED 1104 may be placed outside of the integrating sphere 1102 within a port tube connected to the integrating sphere 1102. Similar to the port tube 405, described above with respect to FIG. 4B, the port tube may be configured (e.g., shaped, sized, and / or oriented) such that the light emitted by the LED 1104 is reflected one or more times off of the internal surface of the integrating sphere 1102 before it exists an output port of the integrating sphere 1102. The internal surface of the integrating sphere may be coated with reflective coating configured to reflect more than 95% of the incident light. In some cases, the internal reflective surface may comprise a Lambertian or Lambertian-like reflective surface. In some cases, the self-calibration of the transfer- standard radiometer using the ILS may comprise an automatic or semi-automatic self-calibration process where a spectroradiometer and the transfer-standard radiometer (e.g., a photonic dosimeter) are positioned at a reference plane at a specified normal distance from the exit port of the light source, so that the sensor signal output by the transfer- standard radiometer is calibrated with respect to the reading of the spectroradiometer.

[0173] FIG. 11 illustrates an example of a bench-top ILS setup 1100 which can be a dedicated experimental setup 1100 for calibrating a photonic dosimeter 122 used to monitor and / or control optical output power of a therapeutic light source. In some cases, the photonic dosimeter can be spectrally matched to the therapeutic light source and the light source of the ILS setup 1100. In some cases, the photonic dosimeter 122 may comprise a photonic dosimeter probe 122a placed at an irradiance measurement plane of the bench-top ILS setup 1100 positioned at a normal distance Lc from a light source of the ILS setup 1100.

[0174] In some cases, the ILS 1100 may comprise the following components:

[0175] 1. The light source formed by an integrating sphere 1102 and an LED 1104:• The integrating sphere may have a diameter from 2” to 10”, e.g., 3”, 4”, or 6”, depending on the size of the photonic dosimeter 1112 (e.g., the size of the corresponding photonic dosimeter probe).• Internal Coating of the integrating sphere: a coating with high reflectivity over a broad band greater than or equal to the bandwidth of the LED 1104 and, in some cases, configured to provide Lambertian-like reflectivity.• Exit port of the integrating sphere: diameter of 1 / 2" or 2-1 / 2", designed forLambertian emission.-M-• Input port for receiving emission from LED 1104: Positioned to block the direct view of the LED from the exit port, ensuring diffuse, uniform output.• Mounting interface and holder: can be designed for a fixed 30 cm calibration distance to the measurement plane.• LED Light Source 1104 with peak wavelengths: selectable LEDs at 460 nm, 465nm, 470 nm, 475 nm, 480 nm, 485 nm, each with a ±2 nm tolerance.

[0176] 2. Thermal management: integrated active heat sink or thermoelectric cooler (TEC) to maintain spectral stability of the LED 1104.

[0177] 3. Electronics:• Power Supply 1108: Power supply for the LED driver and the Microcontroller.• Microcontroller 1110: can be an Arduino-based microcontroller with a touch screen display and PWM functions.• LED Driver 1106: Constant current, low-noise operation to ensure stability.

[0178] The microcontroller 1110 may function as the system’s embedded control unit, generating pulse-width-modulation (PWM) signals that drive the LEDs and create precisely regulated photonic flux within the integrating sphere. Additionally, it may allow fine- tuning of irradiance (therapeutic dosages) based on a newborn’s gestational age, bilirubin levels, and dosage requirements (Irradiance x Time) based on Body Surface Area (BSA).

[0179] Spectral irradiance from ILS will be measured at distances of Lc = 30 cm, 40 cm, 50 cm, and 60 cm to evaluate conformity to the inverse-square law and assess beam uniformity across these distances.

[0180] In the experimental setup 1100, a 475 nm LED light source 1104 is driven by a driver 1106 in response to receiving driver signal (e.g., pulse-width modulated signal) from a microcontroller 1110 (which may have a display). During the ILS calibration phase, the microcontroller 1110 may be programmed with irradiance reference values obtained from a calibrated spectroradiometer positioned at the irradiance-measurement plane which may be separated from the light source by a distance Lc. This may allow the ILS to function as a programmable optical reference capable of generating stable, repeatable irradiance levels.

[0181] Light from the LED 1104 enters the integrating sphere 1102, where multiple internal reflections and a central baffle create a highly uniform, diffuse light field. Using theintegrating sphere in this manner transforms the ILS into a metrology-grade calibration platform, ensuring spatial uniformity and spectral stability essential for accurate radiometric calibration. The diffuse light exits through the integrating sphere’s port and travels along a defined 30 cm optical path toward the irradiance-measurement plane.

[0182] At this plane, the calibrated spectroradiometer first records precise spectral irradiance values across the bilirubin-absorption band. These measurements establish the reference dataset used to program and validate the ILS output. Once the ILS’s irradiance levels are verified, the SBPS radiometer probe is placed in the same geometry and exposed sequentially to the same irradiance settings.

[0183] By comparing the dedicated radiometer’s electrical output to the spectroradiometer’ s reference values, correction coefficients are derived for each radiometer. These coefficients may ensure that every photonic dosimeter reports true spectral irradiance (pW / cm2 / nm) at the bilirubin-absorption peak (-475 nm), regardless of LED spectral variations or device-to-device differences.

[0184] This two-stage calibration process — first calibrating the ILS with a spectroradiometer, then calibrating SBPS radiometers against the ILS — provides full traceability, accuracy, and reproducibility for all irradiance measurements used in SBPS development, validation, and clinical operation.

[0185] In some cases, a cuvette with bilirubin serum can be placed at the irradiancemeasurement plane for photodegradation testing under spectroradiometer-verified irradiance.

[0186] In some cases, the ILS setup shown in FIG. 11 may be used to calibrate and / or measure the irradiance of an illumination unit or a group of illumination units of a light box (e.g., light box 210 or 410). In these cases, the integrating sphere of the ILS setup may be replaced with the illumination unit or the group of illumination units.Phototherapy experiment with real time monitoring of a circulating sample

[0187] In some cases, it can be useful to study the effect of therapeutic illumination on a liquid sample (e.g., blood serum) as it circulates through a dynamic cuvette system. In some embodiments, an experimental platform may be configured to illuminate a liquid sample circulating within a dynamic cuvette system using a small therapeutic light source (e.g., comprising one or more illumination light units of the light box 210 or 410) to providemeasurements that may account for biological variability of the illuminated sample and a medium through which the therapeutic light may be transmitted before being absorbed by the sample. In some cases, these measurements may be used to build an evidence-based phototherapy model for delivering a precise dose of therapeutic light during a phototherapy session.

[0188] FIG. 12A schematically illustrates a side cross-sectional view of an example experimental setup 1200 for (12A) for illuminating a liquid sample flowing through a cuvette 1206 using a calibrated therapeutic light source 1202. FIG. 12B schematically illustrates a side cross-sectional view of an example sample circulation system 1201 configured to circulate a liquid sample between the cuvette 1206 and a sample reservoir 1212. In some cases, the experimental setup 1200 may comprise the following features / elements:• A therapeutic light source 1202 with tunable and calibrated spectral irradiance (e.g., adjustable from 20 to 70 pW / cm2 / nm at a specified distance, Lt), and a center wavelength (1c), for example 475 nm, and controllable emission bandwidth (e.g., FWHM of about 20 nm). In some cases, the therapeutic light source 1202 may comprise one or more illumination units (e.g., the illumination units of the light box 210 or 400) configured to generate therapeutic light having uniformly distributed irradiance over an exit aperture.• A cuvette 1206 configured to allow light emitted by the therapeutic light source 1202 provide to interact with the sample longitudinal flowing through the cuvette 1206, along a transverse optical path length, which can be substantially normal to the flow. In some cases, the optical path can be substantially equal to 1 millimeter. In some cases, the optical path (e.g., eth optical interaction length) can be from 0.5 millimeter to 0.7 millimeter, form 0.7 millimeter to 1 millimeter, from 1 millimeter to 1.3 millimeter, from 1.5 millimeter, from 1.5 millimeter to 2 millimeter, or any ranges formed by these values or larger or smaller values. In some cases, the cuvette 1206 may comprise a puck or thin cylinder having a thickness substantially to the optical path length and a diameter ranging from 1 cm to 2 cm (e.g., 1.5 cm). In some cases, the therapeutic light can become incident (e.g., near normally) on a major face of the cuvette 1206, pass through the thickness of the cuvette 1206 (where it interacts with flowing sample), and exits from the opposite major face of the cuvette.• A liquid sample comprising human serum, e.g., with a bilirubin concentration of 20 mg / dL, flowing through the cuvette 1206.• A sample circulation system 1201 configured to provide a modulated sample flow rate (Q) via the cuvette 1206. In some cases, the flow rate (Q) may be determined based on estimated skin blood flow, as calculated from gestational age (GA), weight, and length of the neonate. In some cases, the sample circulation system 1201 configured.• Bilirubin degradation measurement in real time at the cuvette output (TcB) and periodically in the serum reservoir (TsB).• A skin-mimicking optical membrane material 1210 placed on the cuvette 1206 such that TcB -based monitoring can be performed via the skin-mimicking optical membrane material 1210, e.g., using a jaundice meter (e.g., an optical non-invasive bilirubin measurement device). In some cases, the skin-mimicking optical membrane material 1210 may be placed on a side of the cuvette 1206 through which light exits the cuvette 1206. In some such cases, therapeutic light may interact with the sample without interacting with the skin-mimicking optical membrane material 1210. In some embodiments, the skin-mimicking optical membrane material 1210 may be placed on the cuvette 1206 to measure TcB after illuminating the sample with the therapeutic light.• The sample (serum) reservoir 1212 filled as per the GA age of the neonatal patient.

[0189] In some embodiments, the experimental setup 1200 may be used to characterize the relation between bilirubin concentration in a circulating sample (e.g., human serum) and irradiance of therapeutic light provided to the circulating sample

[0190] The experimental setup may closely mimic neonatal skin perfusion and bilirubin transport under phototherapy. Unlike static in vitro tests, the dynamic flow of the illuminated sample may reflect the continuous perfusion of bilirubin-rich serum across illuminated skin and allow for real-time evaluation of the effect of illumination by therapeutic light. By varying irradiance and / or spectral profile of the therapeutic light provided to circulating sample, and flow rate of the sample, the measurements obtained by the experimental setup 1200 may be used to:Optimize phototherapy protocols tailored to gestational age and clinical status Inform future Al-assisted control systems for phototherapy devices• Photodegradation Modeling may validate bilirubin dose-response model through in vitro photodegradation studies and enables the development of clinically relevant light dosing protocols.Application of the standardized phototherapy system

[0191] Given that light emitting diodes can emit light at wavelength raging from ultraviolet (e.g., 308 - 311 nm) to the visible spectrum and to infrared light (e.g., near-infrared light having wavelength from 850 nm - 1500 nm), the principles and methods described below, which enable delivery of therapeutic light having a spatially uniform and calibrated irradiance to a treatment region, can be extended into many medical and cosmetic applications far beyond bilirubin therapy. Example applications can include:

[0192] 1. Dermatological Phototherapy (308-311 nm Narrowband UVB)• Psoriasis, vitiligo, and eczema treatment• Homogeneous UVB field eliminates local overexposure and burning• Integrated 310 nm radiometer provides controlled dose (mJ / cm2) rather than time-based approximation• Existing products have no real-time irradiance validation

[0193] 2. Acne and Cosmetic Blue-Red Combination Therapy (415 nm + 630 nm)• Blue light for P. acnes• Red light for anti-inflammatory and cosmetic rejuvenation• SBPS allows dual-channel balancing with closed-loop dose monitoring

[0194] 3. Tanning and Cosmetic UV Systems (305-365 nm)• Current tanning beds deliver inconsistent UVA / UVB output and lack any calibrated measurement.• Standardized phototherapy system enables:• Controlled UV output• Homogeneous facial / body exposure• UVA (365 nm) and UVB (305 nm) LED modules with feedback sensor• Prevention of localized overexposure (“hot spots”)

[0195] 4. Retinal, Ophthalmic, and Circadian Therapy (460-500 nm)• Melanopsin-targeted circadian lighting• Blue-light ophthalmic research• Applications requiring uniform, low-dose exposure

[0196] 5. Neonatal and Pediatric Light-Based Devices (470-510 nm)• SBPS core bilirubin system (475 nm)• TcB reflectance module (470-510 nm)

[0197] 6. Photobiomodulation & Wound Healing (630-850 nm)• Red (630-660 nm) and NIR (810-850 nm) therapies for pain, tissue repair, hair growth, orthopedics• Current devices lack field uniformity and dose accuracy• SBPS can deliver consistent fluence (J / cm2) through closed-loop regulation

[0198] 7. Dental & Oral Photodynamic Therapy (630-680 nm)• Gingival infection and periodontal therapy• Standardized phototherapy system enables fiber-optic or handheld uniform illumination Integrated radiometry is unprecedented in current dental PDT

[0199] 8. Cancer Photodynamic Therapy (635-710 nm)• ALA / PpIX, methylene blue, chlorin-based PDT• Highly sensitive to correct wavelength and uniform dose• SBPS architecture ideal for oncology applications

[0200] 9. Blood I Photopheresis I UVA-Psoralen Activation (320-400 nm)• Standardized phototherapy system can deliver uniform UVA exposure across flow-through cuvettes• Current systems have no in-line irradiance measurement

[0201] In various implementations, the above referenced applications may benefit from one or more features of the standardized phototherapy system described with respect to FIGS. 1-12:• identical control logic (PWM modulation),• uniformity-based optical architecture,• calibrated radiometer linked to the LED spectrum,• closed-loop adjustment of irradiance, and• modular design (subassemblies interchangeable by wavelength),Phototherapy control and monitoring: software interface

[0202] The computing system 114 can serve as the clinical command interface for the standardized phototherapy system 100 (e.g.. a bilirubin phototherapy system). In some cases, a processor of the computing system 114 may execute machine readable instructions to integrate patient demographics and physiologic parameters (GA, weight, skin type), essential laboratory data (TSB, Hb, Het, Albumin), and real-time irradiance feedback from the phototherapy device into a unified control platform. Such control platform may be used to control, monitor, and / or analyze the phototherapy treatment provided to a patient by a phototherapy system (e.g., phototherapy system 100).

[0203] In some cases, computing system 114 may execute readable machine instructions to generate a number of dedicated screens or windows to guide clinicians through the phototherapy process. In some cases, individual ones of six dedicated windows may provide an overview of a phototherapy cases, process or session (case summary and status), allow a user to provide patient data and record, provide clinical data & lab values, display a phototherapy treatment graph, display epidemiological data, and control and / or monitor a selfcalibration process (e.g., a self-calibration process to calibrate the irradiance provided by the light source). Together, these windows may enable continuous monitoring, algorithm-based irradiance modulation, and automatic documentation of treatment outcomes.

[0204] In some embodiments, the photonic-dosage parameters displayed on the user interface (e.g., display of the computing system 114) are referenced to preliminary calibration data derived from the irradiance laboratory standard (ILS) described above with respect to FIG. 11. In some examples, photonic dosage parameters may comprise exposure time and irradiance of therapeutic light at the treatment region. The ILS may functions as an in-vitro reference framework that enables accurate conversion of measured irradiance into true spectral irradiance at the clinically effective wavelength (-475 nm). These reference values may guide photonic-dosage adjustments and promote traceable and reproducible measurements during ongoing development and validation.

[0205] As described above earlier AAP phototherapy guidelines defined “intensive phototherapy” as delivering > 30 pW / cm2 / nm in the 430-490 nm band — values derived from clinical consensus rather than standardized radiometric experiments. However, measurements were made with radiometers not spectrally matched to broad fluorescent or early LED sources,resulting in significant variability in true delivered irradiance and inconsistent clinical performance.

[0206] In contrast, the signal and data (e.g., calibration data) generated by the phototherapy systems and methods described above can link ILS -referenced calibration data with real-time bilirubin trends (TcB vs Time) and physiological inputs to modulate irradiance dynamically within a protective (hormetic) therapeutic zone. While the ILS remains a laboratory-based reference, its incorporation into SBPS establishes the first pathway toward standardized, feedback-controlled phototherapy dosage — providing both measurable safety advantages and a foundation for ALassisted treatment optimization and future clinical standardization.

[0207] FIGS. 13-34 schematically illustrates different screens generated by a computing system configured to receive patient data and determine, control and / or monitor different parameters associated with phototherapy provided to a patient by a phototherapy system.

[0208] The screens shown in FIGS. 13-15 are example screens (views) of an overview window that provide a live dashboard of ongoing phototherapy activity across all patients, it shows the total number of patients under care, new intakes, and those flagged as critical. A simple, color-coded status bar indicates which patients are currently receiving therapy, under observation, or have been discharged. It gives clinicians an instant snapshot of workload and treatment progress.

[0209] The screens shown in FIGS. 16-17 are example screens (views) of a patient intake and record window used at the start of treatment to enter and view basic patient details and admission data, it confirms identifiers such as name, gestational age, weight, sex, and current age in hours or days, along with the clinical assessment of jaundice severity. Once saved, these parameters automatically populate the following screens for dosage and tracking consistency.

[0210] The screens shown in FIGS. 18-21 are example screens (views) of a clinical data & lab values window displaying the key laboratory results relevant to phototherapy response — total serum bilirubin (TsB), transcutaneous bilirubin (TcB), hematocrit, hemoglobin, and albumin, it presents values chronologically so changes can be seen at aglance. This may form the baseline dataset for the algorithm that determines irradiance adjustment during treatment.

[0211] The screens shown in FIGS. 22-29 are example screens (views) of a phototherapy treatment window which is a graphical treatment monitor showing TcB versus time on a scrolling chart. The algorithm guides irradiance level adjustments: higher output when bilirubin is high, progressively reduced as levels decline, for instance. TcB above 18 mg / dl triggers stronger irradiance (30-45 pw / cm2 / nm, ILS-referenced); between 18-12 mg / dl, output is -75%; below 12 mg / dl, reduced to 50%; and therapy pauses if TcB falls under 5 mg / dl. If TcB rises again, irradiance is proportionally restored. This dynamic modulation may keep light exposure within a protective (hermetic) range, preventing over- or under-treatment.

[0212] The screens shown in FIGS. 30-32 are example screens (views) of an epidemiological data window that may aggregate de-identified performance metrics — total treated patients, success rate, average treatment duration, and other outcome statistics. The summary data shown on the epidemiological data window may allow continuous improvement, clinical benchmarking, and the creation of research datasets that will ultimately inform ai-driven optimization and population-level phototherapy guidelines.

[0213] The screens shown in FIGS. 33-34 are example screens (views) of a selfcalibration window that may verify the light source output and confirm sensor calibration against the internal reference (ILS-derived baseline). This window reports actual measured irradiance, uniformity across the treatment field, and lamp stability over time. This feature ensures every phototherapy session begins with a known and validated light intensity, supporting reproducible and safe clinical performance.Example embodiments

[0214] Various additional example embodiments of the disclosure can be described by the following clauses:

[0215] Clause 1. A system for providing bilirubin phototherapy to a treatment region of a pediatric patient, the system comprising: a light box comprising a plurality of illumination units arranged in a matrix and an output window configured to cover output apertures of the plurality of illumination units, wherein each of the plurality of illumination units comprises:at least one light emitting diode (LED), configured to emit therapeutic light within a bandwidth around a peak therapeutic wavelength; and an optical reflector configured to reflect at least a portion of the therapeutic light emitted by the at least one LED, wherein the at least one LED is positioned to directly emit light, and wherein the optical reflector is configured to reflect the therapeutic light towards the output window, and wherein the output window has a reflectance greater than or equal to 50% at the peak therapeutic wavelength; a photonic dosimeter configured to be positioned in proximity to the treatment region or an expected treatment region, wherein the photonic dosimeter is configured to generate an irradiance signal indicative of irradiance of a portion of the emitted therapeutic light incident on the treatment region or an expected treatment region, the photonic dosimeter comprising: a second LED configured to generate a sensor signal in response to receiving the portion of the emitted therapeutic light, wherein the second LED is substantially identical to the at least one LED; and a readout circuit comprising an averaging circuit, the readout circuit configured to receive the sensor signal and generate the irradiance signal based on the sensor signal; and a controller configured to generate a driver signal, the driver signal configured to control irradiance of the emitted therapeutic light, wherein the irradiance of the emitted light is calibrated based on the irradiance signal.

[0216] Clause 2. The system of clause 1, further comprising at least one driver configured to receive the driver signal and provide a drive current to the at least one LED to generate the therapeutic light.

[0217] Clause 3. The system of any one of clauses 1-2, wherein the driver signal is pulse width modulated signal having a duty cycle, and wherein the irradiance of the light is controlled by the duty cycle.

[0218] Clause 4. The system of any one of clauses 1-2, wherein the at least one driver comprises first and second drives configured to provide first and second driver signalsto first and second illumination units of the plurality of illumination units, respectively, wherein a difference between the first and second driver signal is configured to reduce a spatial variation of the irradiance over the treatment region or the expected treatment region.

[0219] Clause 5. The system of any one of clauses 1-4, wherein the controller is further configured to: determine an irradiance value based on the driver signal, a normal distance between the output window and the treatment region or the expected treatment region, and calibration data stored in a non-transitory memory, and display the irradiance value on a user interface, wherein the calibration data comprises a reference relationship between the driver signal and a measured irradiance at the normal distance.

[0220] Clause 6. The system of clause 5, wherein the user interface is a touch sensitive display.

[0221] Clause 7. The system of any one of clause 5-6, wherein the calibration data is generated using the irradiance signal during a calibration period.

[0222] Clause 8. The system of any one of clauses 5-8, wherein the normal distance is provided by a user via the user interface.

[0223] Clause 9. The system of clause 5, wherein the system is in wired or wireless communication with a computing system comprising the user interface.

[0224] Clause 10. The system of clause 9, wherein the computing system comprises laptop, a tablet, a personal computer, or a smartphone.

[0225] Clause 11. The system of any one of clauses 1-10, wherein the photonic dosimeter does not include an optical filter.

[0226] Clause 12. The system of any one of clauses 1-11, wherein a reflecting surface of the reflector comprises a reflective coating configured to reflect at least 95% of the received portion of the therapeutic light.

[0227] Clause 13. The system of any one of clauses 1-12, wherein the reflector comprises a parabolic or hemispherical reflector.

[0228] Clause 14. The system of any one of clauses 1-13, wherein the peak therapeutic wavelength is between 470 nm and 480 nm.

[0229] Clause 15. The system of clauses 14, wherein the peak therapeutic wavelength is 475 nm.

[0230] Clause 16. The system of any one of clauses 1 -15, wherein the therapeutic bandwidth is less than 25 nm.

[0231] Clause 17. The system of any one of clauses 1-15. wherein the therapeutic bandwidth is from 18 nm to 24 nm.

[0232] Clause 18. The system of any one of clauses 1-17, wherein the controller is in wired or wireless communication with a computing system, the computing system comprising a non-transitory memory storing machine-readable instructions and a hardware processor configured to execute the machine-readable instructions to: receive patient data a user or a remote computing system via a wired or wireless link; determine a target irradiance based on the patient data; and control the driver signal to deliver the target irradiance to treatment region, wherein the patient data is associated with the pediatric patient.

[0233] Clause 19. The system of clause 18, wherein the hardware processor is further configured to determine a target phototherapy time based on the patient data and control the driver signal to deliver the target irradiance during the determined target phototherapy time.

[0234] Clause 20. The system of any one of clauses 18-19, wherein the remote computing system comprises a medical record system.

[0235] Clause 21. The system of any one of clause 18-20, wherein the patient data comprises one or more of a biochemical parameter of the pediatric patient, a physical parameter of the pediatric patient, and a physiological parameter of the pediatric patient.

[0236] Clause 22. The system of clause 21 wherein the biochemical parameter of the pediatric patient comprises a bilirubin level or concentration.

[0237] Clause 23. The system of any one of clauses 1-22, wherein the photonic dosimeter transmits the irradiance signal to the controller via a wired or wireless link.

[0238] Clause 24. A phototherapy system for providing therapeutic light to a patient, the phototherapy system comprising: a first light emitting diode (LED) configured to emit the therapeutic light having wavelengths within a therapeutic bandwidth around a peak therapeutic wavelength; and a photonic dosimeter configured to receive the therapeutic light and generate an irradiance signal indicative of irradiance of the therapeutic light, the photonic dosimeter comprising: a second LED configured to generate a sensor signal in response to receiving the therapeutic light, wherein the second LED is substantially identical to the first LED; and a readout circuit comprising an averaging circuit, the readout circuit configured toreceive the sensor signal and generate the irradiance signal based on the sensor signal. Tn cases, one or both the peak emission wavelength and bandwidth (e.g., full-width-half-max) of the second LED can be identical or substantially identical to those of the first LED.

[0239] Clause 25. The phototherapy system of clause 24, wherein the peak therapeutic wavelength is about 475 nm.

[0240] Clause 26. The phototherapy system of any one of clauses 24-25, wherein the therapeutic bandwidth is less than 25 nm.

[0241] Clause 27. The phototherapy system of any one of clauses 24-26, wherein the first LED comprises a first PN junction configured to generate the therapeutic light upon receiving electric current and the second LED comprises a second PN junction configured to generate the sensor signal upon receiving the therapeutic light, and wherein the first PN junction is substantially identical to the second PN junction.

[0242] Clause 28. A photonic dosimeter configured to receive incident light and generate an irradiance signal indicative of irradiance of the light, the photonic dosimeter comprising: A light emitting diode (LED) configured to generate a sensor signal in response to receiving the incident light; and a readout circuit configured to receive the sensor signal and generate the irradiance signal based on the sensor signal.

[0243] Clause 29. The photonic dosimeter of clause 28, wherein the readout circuit comprises an averaging circuit.

[0244] Clause 30. The photonic dosimeter of any one of clauses 28-29, wherein the received incident light comprises wavelengths within a bandwidth around a peak incident wavelength, and wherein upon being driven by an electric current, the LED generates light having a peak emission wavelength within ± 1% of the peak incident wavelength.

[0245] Clause 31. The photonic dosimeter of clause 30, wherein the bandwidth of the incident light is less than 25 nm.

[0246] Clause 32. The photonic dosimeter of any one of clauses 30-31, wherein the bandwidth of the incident light is less than 50 nm.

[0247] Clause 33. The photonic dosimeter of any one of clauses 30-32, wherein the peak incident wavelength is about 475 nm.Terminology

[0248] Although these inventions have been disclosed in the context of certain embodiments and examples, it will be understood by those skilled in the art that the present inventions extend beyond the specifically disclosed embodiments to other alternative embodiments and / or uses of the inventions and obvious modifications and equivalents thereof. In addition, while several variations of the inventions have been shown and described in detail, other modifications, which are within the scope of these inventions, will be readily apparent to those of skill in the art based upon this disclosure. Furthermore, various applications of such embodiments and modifications thereto, which may occur to those who are skilled in the art, are also encompassed by the general concepts described herein. Optional features of various device and system embodiments may be included in some embodiments and not in others. The foregoing description is provided primarily for exemplary purposes and setting forth specific details of various embodiments; therefore it should not should not be interpreted to limit the scope of the invention as it is set forth in the claims.

[0249] It should be understood that various features and aspects of the disclosed embodiments can be combined with or substituted for one another in order to form varying modes of the disclosed inventions. Each and every feature described herein, and each and every combination of two or more of such features, is included within the scope of the present invention provided that the features included in such a combination are not mutually inconsistent.

[0250] The limitations in the claims are to be interpreted broadly based on the language employed in the claims and not limited to the examples described in the present specification or during the prosecution of the application, which examples are to be construed as non-exclusive.

[0251] Although various illustrative embodiments are described above, any of a number of changes may be made to various embodiments without departing from the scope of the invention as described by the claims. For example, the order in which various described method steps are performed may often be changed in alternative embodiments, and in other alternative embodiments one or more method steps may be skipped altogether.

[0252] While the above detailed description has shown, described, and pointed out novel features as applied to various examples, it will be understood that various omissions,substitutions, and changes in the form and details of the devices illustrated can be made without departing from the spirit of the disclosure. As will be recognized, the inventions described herein can be embodied within a form that does not provide all of the features and benefits set forth herein, as some features can be used or practiced separately from others.

[0253] For purposes of this disclosure, certain aspects, advantages, and novel features are described herein. It is to be understood that not necessarily all such advantages may be achieved in accordance with any particular embodiment. Thus, for example, those skilled in the art will recognize that the disclosure may be embodied or carried out in a manner that achieves one advantage or a group of advantages as taught herein without necessarily achieving other advantages as may be taught or suggested herein.

[0254] Conditional language used herein, such as. among others, "can," "might," "may," “for example,” and the like, unless specifically stated otherwise, or otherwise understood within the context as used, is generally intended to convey that certain examples include, while other examples do not include, certain features, elements and / or states. Thus, such conditional language is not generally intended to imply that features, elements and / or states are in any way required for one or more examples or that one or more examples necessarily include logic for deciding, with or without author input or prompting, whether these features, elements and / or states are included or are to be performed in any particular example. The terms “comprising,” “including,” “having,” and the like are synonymous and are used inclusively, in an open-ended fashion, and do not exclude additional elements, features, acts, operations, and so forth. Also, the term “or” is used in its inclusive sense (and not in its exclusive sense) so that when used, for example, to connect a list of elements, the term “or” means one, some, or all of the elements in the list. Further, the term “each,” as used herein, in addition to having its ordinary meaning, can mean any subset of a set of elements to which the term “each” is applied.

[0255] Terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. For example, as used herein, the singular forms “a”, “an” and “the” are intended to include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms “comprises” and / or “comprising,” when used in this specification, specify the presence of stated features, steps, operations, elements, and / or components, but do not preclude thepresence or addition of one or more other features, steps, operations, elements, components, and / or groups thereof. As used herein, the term “and / or” includes any and all combinations of one or more of the associated listed items and may be abbreviated as “ / ”.

[0256] Although the terms “first” and “second” may be used herein to describe various features / elements (including steps), these features / elements should not be limited by these terms, unless the context indicates otherwise. These terms may be used to distinguish one feature / element from another feature / element. Thus, a first feature / element discussed below could be termed a second feature / element, and similarly, a second feature / element discussed below could be termed a first feature / element without departing from the teachings of the present invention.

[0257] Disjunctive language such as the phrase “at least one of X, Y, or Z,” unless specifically stated otherwise, is otherwise understood with the context as used in general to present that an item, term, etc., may be either X, Y, or Z, or any combination thereof (for example, X, Y, and / or Z). Thus, such disjunctive language is not generally intended to, and should not, imply that certain examples require at least one of X, at least one of Y, or at least one of Z to each be present.

[0258] All figures, tables, and appendices, as well as patents, applications, and publications, referred to above, are hereby incorporated by reference. Additionally, all publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application was specifically and individually indicated to be incorporated by reference.

[0259] Some embodiments have been described in connection with the accompanying drawing. However, it should be understood that the figures are not drawn to scale. Distances, angles, etc. are merely illustrative and do not necessarily bear an exact relationship to actual dimensions and layout of the devices illustrated. Components can be added, removed, and / or rearranged. Further, the disclosure herein of any particular feature, aspect, method, property, characteristic, quality, attribute, element, or the like in connection with various embodiments can be used in all other embodiments set forth herein. Additionally, it will be recognized that any methods described herein may be practiced using any device suitable for performing the recited steps.

[0260] In this description, references to "an embodiment," "one embodiment," or the like, mean that the particular feature, function, structure or characteristic being described is included in at least one embodiment of the technique introduced herein. Occurrences of such phrases in this specification do not necessarily all refer to the same embodiment. On the other hand, the embodiments referred to are also not necessarily mutually exclusive.

[0261] In some cases, “infrared (IR) wavelength ranges” may be divided into three ranges termed near-IR, mid-IR, and far-IR wavelength ranges. In some cases, an IR or an NDIR gas sensor or spectrometer may correspond to a gas sensor or spectrometer that determines the concentration of a target gas molecule in a gas sample based on absorption wavelength bands of the target molecule in one or more IR wavelength ranges. Further, it should be understood that IR wavelength ranges may include additional ranges, such as shortwavelength infrared and long-wavelength infrared. Generally, although not necessarily, the infrared range of between 1.5 - 6 microns may be used for gas sensing. In addition to its plain meaning, “light” may refer to electromagnetic radiation having a wavelength between, for example, 0.4 to 15 microns spanning visible (0.4 to 0.75 microns), near-IR (0.75 microns to 1.5 microns), mid-IR (1.5 microns to 8 microns) and far-IR (larger than 8 microns) wavelength ranges.

[0262] Several terms are used interchangeably within this description. Each of the terms are intended to have their customary ordinarily understood plain meaning in addition to the meanings described throughout this application. For example, the terms “electromagnetic power”, and “optical power” can be used interchangeably. In addition to their plain meanings, the foregoing terms may refer to amount of electromagnetic energy delivered per unit time (i.e., each second). It should be also understood that “bandwidth” and “frequency band” can be used interchangeably as they both refer to a limited spectral range in a broad spectrum. It should be further understood that “detector”, “light detector” and “photodetector” can be used interchangeably, all referring to a device that generates an electric signal (e.g., current or voltage) proportional to the power of the optical power received by the device.

[0263] For clarity of description, “reflector” or “mirror” can be used interchangeably to refer to an optical element and / or a surface having a reflectivity greater than or equal to about 0.01% and less than or equal to 100%. For example, an optical element and / or a surface having a reflectivity greater than or equal to about 5% and less than or equalto 99%, greater than or equal to about 10% and less than or equal to 90%, greater than or equal to about 15% and less than or equal to 80%, greater than or equal to about 20% and less than or equal to 70%, greater than or equal to about 30% and less than or equal to 60%, or any value in any range / sub-range defined by these values can be considered as a reflector or mirror.

Claims

WHAT IS CLAIMED IS:

1. A system for providing bilirubin phototherapy to a treatment region of a pediatric patient, the system comprising: a light box comprising a plurality of illumination units arranged in a matrix and an output window configured to cover output apertures of the plurality of illumination units, wherein each of the plurality of illumination units comprises: at least one light emitting diode (LED), configured to emit therapeutic light within a therapeutic bandwidth around a peak therapeutic wavelength; and an optical reflector configured to reflect at least a portion of the therapeutic light emitted by the at least one LED, wherein the optical reflector is configured to reflect the portion of the therapeutic light towards the output window, and wherein the output window has a reflectance greater than or equal to 50% at the peak therapeutic wavelength; a photonic dosimeter configured to be positioned in proximity to the treatment region or an expected treatment region, wherein the photonic dosimeter is configured to generate an irradiance signal indicative of irradiance of a second portion of the emitted therapeutic light incident on the treatment region or an expected treatment region, the photonic dosimeter comprising: a second LED configured to generate a sensor signal in response to receiving the portion of the emitted therapeutic light, wherein the second LED is substantially identical to the at least one LED; and a readout circuit comprising an averaging circuit, the readout circuit configured to receive the sensor signal and generate the irradiance signal based on the sensor signal; and a controller configured to generate a driver signal, the driver signal configured to control irradiance of the emitted therapeutic light, wherein the irradiance of the emitted light is calibrated based on the irradiance signal.

2. The system of claim 1, wherein the driver signal is pulse width modulated signal having a duty cycle, and wherein the controller controls the irradiance of the emitted light by adjusting the duty cycle of the driver signal.

3. The system of claim 1 , further comprising at least one driver configured to receive the driver signal from the controller and provide a drive current to the at least one LED to generate the therapeutic light.

4. The system of claim 3, wherein the at least one driver comprises first and second drivers configured to provide first and second driver signals to first and second illumination units of the plurality of illumination units, respectively, wherein a difference between the first and second driver signals is configured to reduce a spatial variation of the irradiance over the treatment region or the expected treatment region.

5. The system of claim 1, wherein the controller is further configured to: determine an irradiance value based on the driver signal, a normal distance between the output window and the treatment region or the expected treatment region, and calibration data stored in a non-transitory memory, and display the irradiance value on a user interface, wherein the calibration data comprises a reference relationship between the driver signal and a measured irradiance at the normal distance.

6. The system of claim 1, wherein the photonic dosimeter does not include an optical filter.

7. The system of claim 1, wherein a reflecting surface of the optical reflector comprises a diffuse reflective coating configured to reflect at least 95% of the received portion of the therapeutic light.

8. The system of claim 1, wherein the optical reflector comprises a parabolic or hemispherical reflector.

9. The system of claim 1, wherein the peak therapeutic wavelength is between 470 nm and 480 nm.

10. The system of claim 9, wherein the peak therapeutic wavelength is about 475 nm.

11. The system of claim 1, wherein the therapeutic bandwidth is less than 25 nm.

12. The system of claim 1, wherein the therapeutic bandwidth is from 18 nm to 24 nm.

13. The system of claim 1, wherein the controller is configured to control the driver signal and the irradiance of the emitted therapeutic light based on a control signal received from a remote computing system via a wired or wireless link, wherein the control signal is generated based at least in part on patient data.

14. The system of claim 13, wherein the patient data comprises one or more of a biochemical parameter of the pediatric patient, a physical parameter of the pediatric patient, and a physiological parameter of the pediatric patient, and wherein the biochemical parameter of the pediatric patient comprises a bilirubin level or concentration.

15. A photonic dosimeter configured to receive incident light and generate an irradiance signal indicative of irradiance of the incident light, the photonic dosimeter comprising: a light emitting diode (LED) configured to generate a sensor signal in response to receiving the incident light; and a readout circuit configured to receive the sensor signal and generate the irradiance signal based on the sensor signal.

16. The photonic dosimeter of claim 15, wherein the readout circuit comprises an averaging circuit.

17. The photonic dosimeter of claim 15. wherein the received incident light comprises wavelengths within a bandwidth around a peak incident wavelength, and wherein upon being driven by an electric current, the LED generates light having a peak emission wavelength within ± 1% of the peak incident wavelength.

18. The photonic dosimeter of claim 17, wherein the bandwidth of the incident light is less than 25 nm.

19. The photonic dosimeter of claim 15, wherein the photonic dosimeter does not include an optical filter.

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