A temperature measuring instrument

Abstract

The application is suitable for the technical field of temperature measurement, and provides a temperature measuring instrument, which comprises a shell, an infrared array sensor, an ambient temperature sensor, a controller and a display, wherein the infrared array sensor, the ambient temperature sensor and the controller are arranged inside the shell. The infrared array sensor is connected with the controller, is used for collecting infrared radiation signals of a superficial artery measuring area of a measured person, converts the infrared radiation signals into an initial temperature matrix, and sends the initial temperature matrix to the controller; the ambient temperature sensor is connected with the controller, is used for collecting an ambient temperature value of an environment where the measured person is located, and sends the ambient temperature value to the controller; the controller is connected with the display, is used for receiving the initial temperature matrix and the ambient temperature value, determining a body temperature value of the measured person according to the initial temperature matrix and the ambient temperature value, and displaying the body temperature value through the display. The temperature measuring instrument can make the measured temperature more reflect the actual temperature of the measured person.

Description

Technical Field

[0001] This application belongs to the field of body temperature measurement technology, and in particular relates to a temperature measuring instrument. Background Technology

[0002] Body temperature, as a core physiological indicator of human health, plays an irreplaceable role in disease prevention, diagnosis, and health management. Accurate temperature measurement can promptly detect fever symptoms, providing crucial information for early screening of infectious diseases (such as influenza), and effectively reducing the risk of disease transmission. In medical settings, temperature monitoring is an important reference for assessing changes in a patient's condition and judging the effectiveness of treatment; in home care, accurate and convenient temperature measurement tools are essential equipment for protecting the health of special populations such as children and the elderly.

[0003] Currently, existing non-contact infrared thermometers can only measure the temperature of one point at a time, and cannot obtain the overall temperature distribution of the forehead. The measured temperature may be lower than the actual body temperature due to misalignment with high-temperature areas, resulting in missed reports. At the same time, single-point measurement is also easily affected by ambient temperature and other factors, leading to inaccurate body temperature measurements. Utility Model Content

[0004] This application provides a thermometer that can solve the problem of low body temperature measurement accuracy caused by existing non-contact infrared thermometers due to their single measurement point, inaccurate positioning, and imperfect environmental temperature compensation.

[0005] This application provides a temperature measuring instrument, including: a housing, an infrared array sensor, an ambient temperature sensor, a controller, and a display, wherein the infrared array sensor, the ambient temperature sensor, and the controller are all disposed inside the housing; The infrared array sensor, connected to the controller, is used to collect infrared radiation signals from the superficial artery measurement area of ​​the subject, convert the infrared radiation signals into an initial temperature matrix, and send the initial temperature matrix to the controller. The ambient temperature sensor is connected to the controller and is used to collect the ambient temperature value of the environment where the subject is located, and send the ambient temperature value to the controller; The controller, connected to the display, is used to receive the initial temperature matrix and the ambient temperature value, and to determine the body temperature value of the subject based on the initial temperature matrix and the ambient temperature value. The display, disposed on the surface of the housing, is used to display the body temperature value.

[0006] In the above technical solution, the housing is further provided with a detection part facing the superficial artery measurement area of ​​the subject.

[0007] In the above technical solution, the detection surface of the infrared array sensor is parallel to the opening end face of the detection part, and the central axis of the detection surface of the infrared array sensor coincides with the central axis of the opening end face of the detection part.

[0008] In the above technical solution, an infrared optical component is further provided at the opening end face of the detection part. The infrared optical component is used to focus the infrared radiation signal of the superficial artery measurement area of ​​the subject onto the detection surface of the infrared array sensor so that the infrared array sensor can collect the infrared radiation signal.

[0009] In the above technical solution, the infrared optical component is further described as a superlens.

[0010] In the above technical solution, the gripping part of the housing is further provided with an inwardly recessed groove with a horizontal bottom side.

[0011] In the above technical solution, the display is further disposed in the inner wall region of the groove.

[0012] In the above technical solution, a switch measurement button is further provided on the grip part of the housing. The switch measurement button is connected to the controller and the power supply respectively, and is used to turn the thermometer on or off.

[0013] In the above technical solution, the switch measurement button is further used to send a measurement start signal to the controller.

[0014] In the above technical solution, the detection part of the shell is further defined as cylindrical.

[0015] The beneficial effects of the embodiments in this application compared with the prior art are: This application provides a thermometer, including: a housing, an infrared array sensor, an ambient temperature sensor, a controller, and a display, wherein the infrared array sensor, the ambient temperature sensor, and the controller are all disposed inside the housing. The infrared array sensor is connected to the controller and is used to collect infrared radiation signals from the superficial artery measurement area of ​​the subject, convert the infrared radiation signals into an initial temperature matrix, and send the initial temperature matrix to the controller. The ambient temperature sensor is connected to the controller and is used to collect the ambient temperature value of the subject's environment and send the ambient temperature value to the controller. The controller is connected to the display and is used to receive the initial temperature matrix and the ambient temperature value, determine the subject's body temperature value based on the initial temperature matrix and the ambient temperature value, and display the body temperature value on the display. This thermometer scans and measures the superficial artery measurement area of ​​the subject using the infrared array sensor, collecting the spatial temperature distribution to form an initial temperature matrix, which can reduce the possibility of inaccurate positioning in single-point measurements; and collects the ambient temperature value using the ambient temperature sensor, and the controller compensates for the initial temperature matrix based on the received ambient temperature value, reducing the influence of ambient temperature on body temperature, so that the measured temperature more accurately reflects the subject's actual temperature. Attached Figure Description

[0016] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0017] Figure 1 This is a schematic diagram of the structure of a temperature measuring instrument provided in one embodiment of this application; Figure 2 This is a schematic diagram of the structure of a temperature measuring instrument provided in another embodiment of this application; Figure 3 This is a schematic diagram illustrating the effect of morphological processing on a target superficial arterial vessel region as provided in an embodiment of this application; Figure 4 This is a schematic diagram illustrating the effect of morphological processing on a target superficial arterial vascular region according to an embodiment of this application.

[0018] The following are the labeling elements in the figure: 1-Thermometer; 10-Housing; 20-Infrared array sensor; 30-Ambient temperature sensor; 40-Controller; 50-Display; 60-Switch measurement button; 11-Detection section; 12-Holding section. Detailed Implementation

[0019] To make the objectives, technical solutions, and advantages of this application clearer, the embodiments of this application will be further described in detail below with reference to the accompanying drawings. The embodiments described with reference to the accompanying drawings are exemplary and intended to explain this application, and should not be construed as limiting this application.

[0020] In the description of this application, it should be understood that the terms "length", "width", "thickness", "top", "bottom", "inner", "outer", "upper", "lower", "left", "right", etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application.

[0021] To facilitate a clear description of the technical solutions of this application, the terms "first" and "second" are used to distinguish identical or similar items with essentially the same function and effect. Those skilled in the art will understand that the terms "first" and "second" do not limit the quantity or execution order, and that the terms "first" and "second" do not necessarily imply that they are different.

[0022] In this application, unless otherwise expressly specified and limited, the terms "connected" and "linked" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0023] In this application, "and / or" is merely a way of describing the relationship between related objects, indicating that three relationships can exist; for example, A and / or B can represent three cases: A existing alone, A and B existing simultaneously, and B existing alone. Additionally, the character " / " in this document generally indicates that the preceding and following related objects have an "or" relationship.

[0024] It should be noted that, in this application, the words "in one embodiment," "exemplarily," and "for example" are used to indicate examples, illustrations, or descriptions. Any embodiment or design described in this application as "in one embodiment," "exemplarily," or "for example" should not be construed as being more preferred or advantageous than other embodiments or designs. Specifically, the use of words such as "in one embodiment," "exemplarily," and "for example" is intended to present the relevant concepts in a specific manner.

[0025] Traditional non-contact infrared thermometers (such as forehead thermometers) typically measure human body surface temperature at a single point. They are significantly affected by ambient temperature and local skin conditions (such as sweating or wind), resulting in a large deviation from the core body temperature, usually exceeding ±1℃.

[0026] Superficial arteries (such as the superficial temporal artery in the forehead and the superficial carotid artery in the neck) are terminal extensions of the aorta and its branches. Their blood originates directly from arterial blood pumped by the heart and is rapidly transported to the superficial artery region via large blood vessels, without sufficient heat dissipation from peripheral tissues along the way. Extensive experimental data shows that the temperature difference between superficial artery blood and the body's core temperature (such as the temperature of blood in the pulmonary artery and aorta) is ≤0.3℃, significantly better than that of body surface temperature (which can differ from core body temperature by 2℃-3℃). Furthermore, superficial arteries are located 2mm-5mm below the skin and are surrounded by connective tissues such as fat and fascia, forming a natural "insulating layer" that effectively buffers fluctuations in ambient temperature. Comparative tests show that under ambient temperature variations of ±5℃, the temperature fluctuation of superficial arteries is only ±0.2℃, while the skin surface temperature fluctuation exceeds ±1.5℃, indicating that superficial artery temperature has a stronger resistance to interference.

[0027] Superficial arteries have blood flow velocities of 30-50 cm / s, with a single blood flow time of less than 0.5 seconds, making them almost unaffected by local tissue metabolic heat or heat dissipation. Venous blood flow is only 1 / 5-1 / 3 the velocity of arterial blood, and after heat exchange with peripheral tissues, its temperature is 1-2°C lower than the body's core temperature. Capillaries, due to their small diameter and slow blood flow, are easily affected by local inflammation and exercise-induced congestion, resulting in temperature fluctuations of ±1°C or more. Therefore, superficial arteries are ideal carriers for transmitting core body temperature signals. Furthermore, superficial arteries meet the anatomical requirement of "subcutaneous depth ≤5 mm," and the epidermis and superficial dermis covering them have weak absorption and scattering of infrared radiation (8μm-14μm band). Extensive experimental and literature data verify that when infrared radiation penetrates this superficial skin structure, the energy attenuation rate is <15%, allowing for effective capture by infrared array sensors and meeting the signal strength requirements for non-contact measurement.

[0028] Therefore, this application provides a thermometer that scans the surface of human skin using an infrared array sensor, locates and measures the temperature of subcutaneous superficial arteries, and utilizes the high correlation between superficial arteries and core body temperature to achieve non-contact, accurate temperature measurement, thus overcoming the accuracy deficiencies of traditional technologies.

[0029] This thermometer measures body temperature in the superficial artery measurement area of ​​the subject. Multiple locations can be selected for the superficial artery measurement area. The selection priority is as follows: (1) Preferred site: Forehead. The forehead is the area with the highest daily exposure. The superficial temporal artery, supratrochlear artery, and supraorbital artery on the forehead have stable courses (symmetrically distributed along the surface of the frontal bone, with an anatomical variation rate of <5%). Infrared array sensors can clearly capture their temperature gradient within a distance of 1cm-3cm (the superficial artery area is 0.8℃-1.2℃ higher than the surrounding tissue). The scanning path (such as from the glabella to the temple) is highly matched with the direction of the blood vessels, and the positioning accuracy rate is over 95%, making it the optimal measurement site.

[0030] (2) Secondary sites: neck, back of hand, and wrist. The temperature difference between the superficial arteries and the surrounding skin in these sites is 0.5℃-1.5℃. The superficial carotid artery in the neck is located in the superficial layer of the sternocleidomastoid muscle, but it is easily obscured by scarves and high-necked clothing, so the actual measurable probability is only 60%-70% of the time. The superficial palmar branch of the radial artery on the back of the hand and the superficial artery in the wrist have smaller diameters (e.g., diameter <2mm) and shift with hand movements (e.g., clenching a fist), so the measurement stability is 15%-20% lower than that of the forehead. For the above sites, the infrared array sensor needs to be switched to a wide field of view (e.g., 60°) to cover the blood vessel distribution range, which may introduce background interference. This is an alternative when the forehead is obscured, but the measurement accuracy is relatively lower than that of the forehead.

[0031] (3) Special scene locations: elbow, etc. The superficial arteries in the elbow (such as branches of the brachial artery) have a relatively large diameter (e.g., 3mm-4mm). The temperature difference between the superficial arteries in this area and the surrounding skin is 0.9℃-1.5℃, and the infrared signal intensity is high, making it suitable for accurate measurement in medical scenarios (such as when the patient is lying flat). However, this area is rarely exposed in daily life, and the operation is not convenient enough, so it is only used as a supplementary measurement option.

[0032] The following is in conjunction with the appendix Figure 1 and attached Figure 2 This embodiment provides a detailed description of a temperature measuring instrument.

[0033] Please see Figure 1 , Figure 1 This is a schematic diagram of the structure of a thermometer provided in an embodiment of this application. The thermometer 1 includes: a housing 10, an infrared array sensor 20, an ambient temperature sensor 30, a controller 40, and a display 50, wherein the infrared array sensor 20, the ambient temperature sensor 30, and the controller 40 are all disposed inside the housing 10.

[0034] Infrared array sensor 20, connected to controller 40, is used to collect infrared radiation signals from the superficial artery measurement area of ​​the subject, convert the infrared radiation signals into an initial temperature matrix, and send the initial temperature matrix to controller 40.

[0035] An ambient temperature sensor 30 is connected to a controller 40 and is used to collect the ambient temperature value of the environment where the subject is located and send the ambient temperature value to the controller 40.

[0036] The controller 40, connected to the display 50, is used to receive the initial temperature matrix and the ambient temperature value, and to determine the subject's body temperature value based on the initial temperature matrix and the ambient temperature value.

[0037] Display 50, located on the surface of housing 10, is used to display body temperature values.

[0038] like Figure 1 As shown, the housing 10 is the external protective structure of the thermometer 1, and is usually made of materials such as plastic or metal. It can accommodate and fix components such as the infrared array sensor 20, the ambient temperature sensor 30, the controller 40, and the display 50. In this embodiment, the material and structure of the housing 10 are not specifically limited.

[0039] The infrared array sensor 20 is a sensor array capable of detecting infrared radiation signals from the surface of an object. This infrared array sensor 20 consists of multiple infrared sensing elements (such as thermopile or pyroelectric sensors). The infrared sensing elements can be arranged in a two-dimensional matrix, and each element can independently detect the infrared radiation signal at a single point. Therefore, the infrared array sensor 20 can simultaneously collect temperature data from multiple points within the measurement area. For example, a 4×4 infrared array sensor contains 16 independent infrared sensing elements, which can simultaneously collect temperature data from 16 points. By performing a horizontal scan of the forehead from the center of the eyebrows to the temples, the detection window coverage area can accurately locate the superficial temporal artery, identify the area with the highest temperature, and exhibit strong anti-interference capabilities with minimal measurement error.

[0040] The superficial artery measurement area refers to the region on the human body surface where superficial arteries are distributed, such as the superficial temporal artery in the forehead and the radial artery in the wrist. Temperature changes in these areas can quickly reflect the body's core temperature. When the measurement area is the superficial temporal artery, its projected width on the body surface is approximately 5mm-8mm. The detection range of a single infrared sensor element is typically 2mm-3mm. Therefore, for example, a 4×4 infrared array sensor would have a total coverage area of ​​approximately 8mm-12mm, which perfectly matches the width of the superficial temporal artery. If the infrared array sensor array is too small (e.g., a 1×4 linear array), its anti-interference capability is weak; blocking even one infrared sensor element may result in the loss of vascular signals, and it is difficult to analyze the highest temperature region by comparing temperatures. Therefore, to ensure measurement accuracy when measuring superficial arteries, a 4×4 array or a larger array can be used for the infrared array sensor. It should be noted that in this embodiment, the specific array value of the infrared array sensor 20 is not limited; an appropriate array of infrared array sensor 20 can be selected based on the location of the superficial artery measurement area.

[0041] In this embodiment, the infrared array sensor 20 acquires temperature distribution information by detecting infrared radiation signals from the superficial artery measurement area (such as the superficial temporal artery) of the subject, and converts the infrared radiation signals into digital signals to form an initial temperature matrix containing multiple temperature points. Finally, the initial temperature matrix is ​​sent to the controller 40 for subsequent processing and analysis. The initial temperature matrix is ​​a two-dimensional rectangle composed of multi-point temperature data collected by the infrared array sensor 20, where each element represents the temperature value of a point within the measurement area, reflecting the temperature distribution of the measurement area. By analyzing the temperature distribution in the initial temperature matrix, the location of the superficial artery can be identified, improving the accuracy of body temperature measurement.

[0042] The ambient temperature sensor 30 is a sensor that can measure the ambient temperature, typically employing principles such as thermistors, thermocouples, or digital temperature sensors. In this embodiment, the ambient temperature sensor 30 can monitor the temperature of the subject's environment in real time, sending the ambient temperature value to the controller 40 for temperature compensation of the initial temperature matrix, thereby improving the accuracy of body temperature measurement.

[0043] The controller 40 is the core control unit of the thermometer 1, typically composed of a microprocessor or digital processor, primarily responsible for data processing, algorithm execution, and system control. In this embodiment, the controller 40 receives the initial temperature matrix from the infrared array sensor 20 and the ambient temperature values ​​from the ambient temperature sensor 30. It processes the initial temperature matrix and combines it with the ambient temperature values ​​to calculate the subject's body temperature. Finally, the calculated body temperature value is sent to the display 50 for display.

[0044] The display 50 is an output device for displaying measurement results. In this embodiment, the display 50 is disposed on the surface of the housing 10. The display 50 can visually display the subject's body temperature in digital or graphical form for easy reading by the user. The body temperature value displayed on the display 50 can be in Celsius or Fahrenheit. Furthermore, depending on design requirements, the display 50 can also display other information such as measurement status, error messages, and ambient temperature.

[0045] It should be noted that in actual application, assuming the measurement site is the superficial temporal artery on the forehead, the user holds the thermometer 1 and aligns the probe window of the thermometer 1 with the forehead area of ​​the subject, 3cm-5cm away from the forehead surface, and then performs a horizontal scan from the center of the eyebrows to the temples, finally reaching the vicinity of the temples, and the subject's body temperature value can be displayed on the display 50.

[0046] It is understood that the thermometer provided in this embodiment includes: a housing 10, an infrared array sensor 20, an ambient temperature sensor 30, a controller 40, and a display 50, wherein the infrared array sensor 20, the ambient temperature sensor 30, and the controller 40 are all disposed inside the housing 10. The infrared array sensor 20 is connected to the controller 40 and is used to collect infrared radiation signals from the superficial artery measurement area of ​​the subject, convert the infrared radiation signals into an initial temperature matrix, and send the initial temperature matrix to the controller 40; the ambient temperature sensor 30 is connected to the controller 40 and is used to collect the ambient temperature value of the environment in which the subject is located and send the ambient temperature value to the controller 40; the controller 40 is connected to the display 50 and is used to receive the initial temperature matrix and the ambient temperature value, determine the subject's body temperature value based on the initial temperature matrix and the ambient temperature value, and display the body temperature value on the display 50. The thermometer 1 uses an infrared array sensor 20 to scan and measure the superficial artery measurement area of ​​the subject, and collects the spatial temperature distribution to form an initial temperature matrix, which can reduce the situation of inaccurate positioning of single-point measurement; and collects the ambient temperature value through the ambient temperature sensor 30. The controller 40 compensates the initial temperature matrix according to the received ambient temperature value, reducing the influence of ambient temperature on body temperature, so that the measured temperature can better reflect the actual temperature of the subject.

[0047] In the optional solutions of this embodiment, such as Figure 2 As shown, Figure 2 This is a schematic diagram of the structure of a temperature measuring instrument provided in another embodiment of this application. For example... Figure 2 In the housing 10, a probe 11 is provided facing the superficial artery measurement area of ​​the subject.

[0048] One end of the housing 10 is a detector 11, and the other end is a grip 12. The detector 11 is a structure designed on the housing 10 facing the superficial artery measurement area of ​​the subject. The end of the detector 11 away from the main body of the housing 10 is an open end face, which can be facing the superficial artery measurement area when measuring body temperature. The detector 11 also has an internal channel to optimize the transmission path of infrared radiation signals.

[0049] In some examples, the detection surface of the infrared array sensor 20 is parallel to the opening end face of the detection section 11, and the central axis of the detection surface of the infrared array sensor 20 coincides with the central axis of the opening end face of the detection section 11.

[0050] The detection surface of the infrared array sensor 20 is the end face that directly receives infrared radiation signals, and it is usually composed of multiple infrared sensing elements arranged in an array. The infrared array sensor 20 can be set in the internal channel of the detection unit 11. The detection surface of the infrared array sensor 20 is parallel and coaxial with the open end face of the detection unit 11. That is, the normal direction of the detection surface of the infrared array sensor 20 is consistent with that of the open end face of the detection unit 11, i.e., the detection surface of the infrared array sensor 20 is parallel to the open end face of the detection unit 11. Moreover, the center point of the detection surface of the infrared array sensor 20 and the center point of the open end face of the detection unit 11 are located on the same axis. This ensures that the detection surface of the infrared array sensor 20 is perpendicular to the measurement area, avoiding errors in temperature calculation by the thermometer due to angular deviation.

[0051] In some examples, an infrared optical component (not shown in the figure) is provided at the opening end face of the detection unit 11. The infrared optical component is used to focus the infrared radiation signal of the superficial artery measurement area of ​​the subject onto the detection surface of the infrared array sensor so that the infrared array sensor can collect the infrared radiation signal.

[0052] Because the infrared radiation signal in the superficial artery measurement area is divergent, and the energy density decreases with increasing distance, and because the detection surface size of the infrared array sensor 20 is limited, directly receiving the infrared radiation signal would result in insufficient signal strength and a low signal-to-noise ratio. Therefore, an infrared optical component can be provided at the opening end face of the detection unit 11. The infrared optical component can focus the infrared radiation signal onto the detection surface of the infrared array sensor 20, forming an infrared radiation signal with higher energy density, thereby enabling the infrared array sensor 20 to acquire the infrared radiation signal.

[0053] In some examples, the infrared optical components are a combination of conventional optical lenses and filters.

[0054] The combination of traditional optical lenses and filters is a common component in infrared optical systems. Traditional optical lenses focus the infrared beam onto the detection surface of the infrared array sensor 20 through curved refraction. Filters allow only specific wavelengths of infrared light to pass through, suppressing background noise and improving the signal-to-noise ratio. Combining traditional optical lenses and filters allows for precise measurement of the temperature of the human body surface, avoiding interference from environmental radiation.

[0055] In some examples, the infrared optical component is a superlens.

[0056] A metalen is a two-dimensional planar lens based on a metasurface. It precisely controls the phase, amplitude, and polarization state of light waves through subwavelength-scale artificial nanostructures, achieving the focusing and imaging functions of a traditional lens. A metalen can achieve complex functions such as focusing and imaging with a single-piece structure, significantly reducing the size and weight of the detector unit 11 while improving the signal-to-noise ratio of infrared radiation signals.

[0057] In some examples, the grip portion 12 of the housing 10 is provided with an inwardly recessed groove with a horizontal bottom side.

[0058] In some examples, the display 50 is positioned in the inner wall region of the recess.

[0059] like Figure 2 As shown, the grip portion 12 is the user's handheld area for the thermometer 1. An inwardly recessed groove is provided in the grip portion 12. The bottom side of the groove is a horizontal surface, which can provide a stable mounting reference surface for the display 50, and can also be used to mount other devices, such as indicator lights.

[0060] In some examples, the display 50 is designed to correspond to the recessed area and can be fixed by various methods such as snaps, adhesives, or magnets, achieving integration between the housing 10 and the display 50. Retaining the display 50 in the recess prevents it from protruding and causing discomfort for the user. Furthermore, positioning the display 50 in the center of the recess allows the user's gaze to naturally focus on the screen when holding the device, reducing user reaction time.

[0061] In some examples, a switch measurement button 60 is provided on the grip portion 12 of the housing 10. The switch measurement button 60 is connected to the controller 40 and the power supply (not shown in the figure) respectively, and is used to turn the thermometer 1 on or off.

[0062] In some examples, the switch measurement button 60 is also used to send a measurement start signal to the controller 40.

[0063] It should be noted that the thermometer 1 in this embodiment also includes a power supply (not shown in the figure). The power supply is the energy supply unit of the thermometer 1 and establishes an electrical connection with the infrared array sensor 20, ambient temperature sensor 30, controller 40, display 50, and switch measurement button 60. The power supply can use two AA batteries as the power source to meet the voltage requirements of the low-power electronic components of the thermometer 1. A battery compartment (made of ABS plastic, with a size suitable for two AA batteries installed in series) is provided inside the housing 10 of the thermometer 1. The battery compartment has built-in metal contact pieces (made of brass to ensure conductivity stability) and is equipped with an anti-reverse installation structure (protruding buckles correspond to the battery polarity to prevent the battery from being installed backwards and causing circuit damage). The battery compartment is integrated inside the grip part 12 of the housing 10 (for example, adjacent to the controller 40 to shorten the wire length and reduce power consumption). A removable battery cover is provided on the surface of the grip part 12 of the housing 10. It is fixed by a buckle design and can be opened without tools to replace the battery. The surface of the battery cover is marked with a battery polarity diagram ("+", "-") to guide the user to install correctly. The power supply path for each component is as follows: the positive output terminal of the battery compartment is connected to the switch measurement button 60, and then connected to the power input terminal of the controller 40. At the same time, it is connected to the power pins of the infrared array sensor 20, the ambient temperature sensor 30, and the display 50 through wire branches; the negative output terminal of the battery compartment is directly grounded to the negative pins of each component, forming a complete power supply circuit.

[0064] like Figure 2 As shown, a switch measurement button 60 is also provided on the grip portion 12 of the housing 10. This switch measurement button 60 is integrated into the grip portion 12 and is connected to the controller 40 and the power supply. The switch measurement button 60 can be used to turn the thermometer 1 on or off, realizing the convenience and safety of thermometer operation. The switch measurement button 60 is located on the grip portion 12, which allows the user to directly trigger it when holding the thermometer with one hand without adjusting the hand posture.

[0065] The switch measurement button 60 also has the function of starting body temperature measurement. When the thermometer 1 is in standby mode, it can respond to the user's long press of the switch measurement button 60 and send a measurement start signal to the controller 40 so that the controller 40 can control the infrared array sensor 20 to collect infrared radiation signals when it receives the measurement start signal.

[0066] In practical applications, for example, when a user uses thermometer 1 to measure the body temperature of a subject's superficial temporal artery on the forehead, the user presses the switch measurement button 60 on thermometer 1 for the first time. Power is supplied to all components in thermometer 1, turning it on and putting it into standby mode. When the user presses the switch measurement button 60 again while the thermometer is in standby mode, the switch measurement button 60 sends a measurement start signal to controller 40. Upon receiving this signal, controller 40 controls infrared array sensor 20 to collect infrared radiation signals, initiating the body temperature measurement. The user then holds thermometer 1 and scans the forehead horizontally from the center of the eyebrows to the temples for 3 seconds. The thermometer 1 will then emit a "beep" sound to indicate that the measurement is complete and display the result on display 50. If thermometer 1 remains inactive for 30 seconds, it will automatically enter a low-power standby mode (at which point only display 50 is powered off). When the user presses the switch measurement button 60 for 3 seconds, the power supply to all components is cut off, and thermometer 1 turns off.

[0067] In some examples, the probe 11 of the housing 10 is cylindrical.

[0068] like Figure 2 As shown, the detection part 11 of the housing 10 is cylindrical. By setting the detection part 11 to a cylindrical shape, the axial symmetry of the infrared array sensor 20, the infrared optical components, and the opening end face of the detection part 11 can be ensured, which can reduce the measurement error caused by optical path offset. In this embodiment, the specific shape of the gripping part 12 of the housing 10 is not limited.

[0069] It should be noted that when measuring the body temperature of a subject using the thermometer 1 provided in this embodiment, the infrared radiation signal from the superficial artery measurement area is focused onto the detection surface of the infrared array sensor 20 by the infrared optical component of the thermometer 1. The infrared array sensor 20 converts the infrared radiation signal into an electrical signal, which is then digitized by an analog-to-digital converter to generate an initial temperature matrix. Simultaneously, the ambient temperature value is obtained by real-time monitoring of the temperature of the subject's environment by the ambient temperature sensor 30. After obtaining the initial temperature matrix and the ambient temperature value, the controller 40 in the thermometer 1 processes the initial temperature matrix and performs temperature compensation using the ambient temperature value to obtain the subject's body temperature value.

[0070] Specifically, in this embodiment, taking the measurement of the superficial temporal artery in the forehead as an example, when performing body temperature measurement, the user holds the thermometer 1 and aligns the detection window with the measurement area of ​​the superficial temporal artery in the forehead of the subject, at a distance of 3cm-5cm from the forehead surface, and performs a horizontal scan, eventually reaching the vicinity of the temple. At this time, the infrared array sensor 20 continuously collects temperature data from different locations on the forehead, transmits it to the controller 40, and uses a specific algorithm to locate the position of the superficial temporal artery and measure the temperature.

[0071] (1) First, since the initial temperature matrix acquired by the infrared array sensor 20 may contain environmental noise, such as interference from body hair and skin folds, a Gaussian filtering noise reduction algorithm is needed to smooth the data and remove high-frequency noise from the original data. Specifically, the initial temperature matrix is ​​set to... , For the number of scanned rows, This refers to the number of scan columns. Assuming the infrared array sensor 20 is a 4×4 array, then the number of scan rows is... Number of columns scanned The initial temperature matrix contains 16 temperature values ​​in 4 rows and 4 columns. Each temperature value corresponds to the measurement result of an infrared sensing element in the infrared array sensor 20. Overall, it can reflect the spatial temperature distribution of the superficial artery measurement area.

[0072] It should be noted that the Gaussian filtering noise reduction algorithm is a linear smoothing filtering algorithm based on Gaussian function weights. It suppresses noise by weighted averaging of neighboring pixel values ​​while preserving the overall trend of temperature distribution.

[0073] The Gaussian filtering noise reduction algorithm used in this embodiment is as follows: ; in, The temperature matrix after filtering and noise reduction is the first... Line 1 The temperature values ​​in the column, The absolute coordinates of the target pixel in the initial temperature matrix acquired by the infrared array sensor 20. This is the row index in the initial temperature matrix. The column index in the initial temperature matrix; For Gaussian kernel function, Here, represents the relative coordinates of the elements in the Gaussian kernel function with respect to the kernel center; a and b are the sizes of the half-windows; if the infrared array sensor is a 4×4 array, then a=1 and b=1 in the above formula, meaning the Gaussian kernel is 3×3 (total row dimension is 2a+1=3, total column dimension is 2b+1=3). In this case, the Gaussian kernel can completely cover the surrounding pixels for convolution calculations. Without exceeding the 20-pixel range of the infrared array sensor, smooth filtering is achieved through reasonable weight allocation, thus preserving temperature gradient information. It should be understood that the filtered and denoised temperature matrix obtained after Gaussian filtering can retain the true temperature difference characteristics between the superficial arteries and the surrounding skin, providing more reliable basic data for subsequent feature extraction.

[0074] (2) After obtaining the filtered and denoised temperature matrix, considering the influence of ambient temperature on the measurement results, it is necessary to perform data correction on the filtered and denoised temperature matrix using a temperature compensation model. The ambient temperature compensation amount is calculated using the constructed temperature compensation model. Then, the temperature matrix after filtering and noise reduction... Compensation amount for ambient temperature The results are added together to obtain the corrected temperature matrix. ,Right now .

[0075] The temperature compensation model is a mathematical model used to eliminate the influence of ambient temperature on the measurement results of infrared sensors. It should be noted that this embodiment provides a method for constructing the temperature compensation model. First, a temperature compensation parameter experimental platform is built in a laboratory environment. A constant temperature unit is set up in the experiment, and the temperature adjustment range of the constant temperature unit is set to 35.0℃~42.0℃ according to the standard GB / T 21416-2008 Medical Electronic Thermometer. This constant temperature unit is used to simulate the typical fluctuation range of human core body temperature.

[0076] During the experiment, an infrared array sensor was used to scan and measure the constant temperature unit, and the following three sets of key data were collected simultaneously: (1) the actual temperature value of the constant temperature unit. The temperature value is calibrated in real time by a high-precision thermocouple with an accuracy of ±0.01℃. (2) Real-time ambient temperature value The temperature value was acquired by a negative temperature coefficient NTC thermistor with an accuracy of ±0.1℃. According to the above standards, in order to meet the temperature requirements of the rated working low temperature test, the rated working high temperature test and the normal working conditions, the ambient temperature range for this experiment was set to -5.0℃ to 50.0℃. (3) The original measured temperature value of the infrared array sensor .

[0077] By dynamically adjusting the ambient temperature (e.g., covering application scenarios from -5.0℃ to 50.0℃), the actual temperature value of the constant temperature unit is adjusted at each ambient temperature point. Values ​​were taken sequentially in 0.1℃ increments within the range of 35.0℃ to 42.0℃, and the corresponding values ​​were recorded simultaneously. and Based on the massive amount of collected data, a temperature compensation model is constructed. The core formula of this temperature compensation model is as follows: ; in, This is the amount of compensation for ambient temperature. This is the actual temperature value of the thermostat unit. This represents the real-time temperature of the environment. This represents the original measured temperature value of the infrared array sensor, i.e., the initial measured temperature value corresponding to the initial temperature matrix. The standard ambient temperature value is 25℃, or 298.15K. The first compensation coefficient, This is the second compensation coefficient. This is the third compensation coefficient.

[0078] in, , , The compensation coefficients to be solved are obtained by fitting the experimental data using the least squares method (where the goodness of fit R0 is 1). 2 ≥0.99).

[0079] It should be noted that the core logic of this temperature compensation model is to find the function model that best reflects the data's patterns by minimizing the sum of squares error between the theoretically calculated value and the actual observed value. In the above temperature compensation model, , , The compensation coefficient needs to be determined. During the experiment, a large number of actual temperature values ​​from the isothermal unit were collected. Real-time ambient temperature value The raw measured temperature value of the infrared array sensor and the corresponding compensation amount for actual ambient temperature. Calculate different using the least squares method , , Theoretical environmental compensation under the combination "and the actual environmental compensation amount" Finally, the combination of compensation coefficients that minimizes the total squared difference is selected, thus determining the first compensation coefficient. Second compensation coefficient Third compensation coefficient The specific values ​​are used to ensure that the temperature compensation model's calculation results are as close as possible to the actual data.

[0080] Here, goodness of fit is an indicator that measures the model's ability to explain real-world data, and its value ranges from 0 to 1. Goodness of fit Rfit 2 The closer the value is to 1, the better the model fits the data; that is, the smaller the deviation between the theoretical calculation and the actual observation. In the experiment provided in this embodiment, the goodness of fit R... 2 A value ≥0.99 indicates that the temperature compensation model provided in this embodiment can explain more than 99% of the variation patterns in the measured data, with less than 1% of the error originating from the model's own bias. This ensures the accuracy of the compensation amount calculated using this temperature compensation model. It is reliable enough to ensure that the calibrated body temperature measurement results meet medical-grade accuracy requirements.

[0081] A series of temperature compensation parameters calculated through the temperature compensation model can be directly used to correct the body temperature measurement results of the infrared array sensor in real-world scenarios, namely: This effectively eliminates the impact of ambient temperature fluctuations on measurement accuracy, ensuring that the final body temperature measurement results meet medical-grade error requirements (the standard specifies repeatability error S≤0.2℃).

[0082] Therefore, through the above experiments, the final temperature compensation model is constructed, namely: ; in, This is the amount of compensation for ambient temperature. To preset the temperature value of the constant temperature unit, This is the ambient temperature value. The initial measured temperature values ​​correspond to the initial temperature matrix. This is the standard ambient temperature value (usually 25℃, or 298.15K). The first compensation coefficient, This is the second compensation coefficient. This is the third compensation coefficient.

[0083] It should be understood that by using a temperature compensation model and ambient temperature values ​​to correct the temperature matrix, the influence of ambient temperature fluctuations on the temperature difference between superficial arteries and skin can be effectively eliminated, thereby improving the accuracy of subsequent analysis and calculations.

[0084] (3) Secondly, after obtaining the corrected temperature matrix, the key features that can distinguish superficial arteries from the surrounding skin are extracted from the corrected temperature matrix, namely, temperature gradient feature values ​​and regional temperature stability feature values. The boundary between superficial arteries and the surrounding skin, i.e., the potential vascular boundary location, can be determined by the extracted temperature gradient feature values ​​and regional temperature stability feature values.

[0085] The temperature gradient feature value represents the temperature difference between adjacent pixels in the corrected temperature matrix, reflecting the temperature distribution trend in the superficial artery measurement area. The regional temperature stability feature value represents the degree of temperature change over time or space within the superficial artery measurement area, distinguishing between dynamic (e.g., blood vessels) and static (e.g., skin) regions. The temperature of superficial arteries in the forehead (e.g., superficial temporal artery, supratrochlear artery) is typically 0.8℃-1.2℃ higher than the surrounding non-vascular skin temperature. The temperature difference between superficial arteries and surrounding skin in areas such as the neck, back of the hand, and wrist is slightly lower, typically 0.5℃-0.9℃. In special areas like the elbow, where the superficial arteries have a larger diameter (e.g., 3mm-4mm), the heat from blood flow is more concentrated, resulting in a temperature difference of 1.0℃-1.5℃ between the superficial arteries and surrounding skin. Experiments have shown that a temperature difference range of 0.8℃-1.2℃ is a typical characteristic of the temperature difference between superficial arteries and surrounding skin, indicating a stable temperature difference. Therefore, a significant temperature gradient exists at the interface between the superficial arteries and surrounding skin, i.e., the temperature gradient feature. Superficial arteries maintain a relatively constant temperature due to continuous arterial blood flow, exhibiting minimal temperature fluctuations. In contrast, the surrounding skin temperature is easily affected by the environment, resulting in greater temperature fluctuations and potentially multiple isolated high-temperature points lacking continuity. Therefore, regional temperature stability characteristics can be used to distinguish superficial arteries from the skin. It should be understood that analyzing temperature gradient characteristic values ​​and regional temperature stability can preliminarily determine the potential location of vascular boundaries.

[0086] After determining the potential vascular boundary location of the superficial artery measurement area of ​​the subject, the high-temperature region is extracted from the potential vascular boundary location of the superficial artery measurement area of ​​the subject according to the adaptive threshold segmentation algorithm and the preset temperature difference value, thereby determining the target superficial artery vascular area.

[0087] The adaptive threshold segmentation algorithm is an algorithm that dynamically adjusts the segmentation threshold based on local image characteristics. It can extract vascular regions with temperatures higher than the surrounding skin within potential vascular boundaries. The preset temperature difference value is the temperature difference between superficial arteries and the surrounding skin, typically between 0.8℃ and 1.2℃.

[0088] It should be understood that by using an adaptive threshold to adapt to local temperature changes, undersegmentation or oversegmentation caused by a global threshold can be avoided, thereby further accurately determining the superficial arterial vessel region.

[0089] Specifically, an edge detection algorithm is used to calculate the comprehensive temperature gradient value. By applying specific convolution kernels in the horizontal (x-direction) and vertical (y-direction) directions respectively, edges of temperature changes are detected, thereby capturing the temperature difference boundary between superficial arteries and surrounding skin, effectively extracting the boundary features between blood vessels and skin. The edge detection algorithm is an image processing algorithm that detects image edges by calculating approximate gradient values ​​for each pixel in the horizontal and vertical directions. In this embodiment, the edge detection algorithm calculates the temperature gradient values ​​of the temperature matrix in the horizontal and vertical directions. The formulas for calculating the horizontal and vertical temperature gradient values ​​are as follows: ; ; in, This represents the temperature gradient value in the horizontal direction. The vertical temperature gradient value; K is the weighting coefficient; For the corrected temperature matrix, the first... line, number Temperature values ​​corresponding to column pixels; For the corrected temperature matrix, the first... line, number Temperature values ​​corresponding to column pixels; For the corrected temperature matrix, the first... +1 line, number Temperature values ​​corresponding to column pixels; For the corrected temperature matrix, the first... -1 line, number Temperature values ​​corresponding to column pixels; For the corrected temperature matrix, the first... line, number Temperature values ​​corresponding to column pixels; For the corrected temperature matrix, the first... +1 line, number Temperature values ​​corresponding to column pixels; For the corrected temperature matrix, the first... +1 line, number Temperature values ​​corresponding to column pixels; For the corrected temperature matrix, the first... -1 line, number Temperature values ​​corresponding to the column pixels.

[0090] By weighting and subtracting the above formulas, the temperature change rates in the horizontal and vertical directions are obtained. For a 4×4 infrared array sensor, when the weighting coefficient K is set to 2, the calculation is guaranteed to be within a limited pixel range, ensuring the overall recognition accuracy. This makes the temperature value near the center have a greater impact on the gradient result (the temperature correlation between the center pixel and its positive neighbors, i.e., the right and left sides, is the strongest, and contributes the most to the gradient change).

[0091] Then, the combined temperature gradient value is calculated using the following formula. The comprehensive temperature gradient value, obtained by combining the horizontal and vertical temperature gradient values, can more comprehensively reflect the temperature variation in two-dimensional space. ; At the boundary between blood vessels and skin, there is a temperature difference of 0.8℃-1.2℃. The value will be significantly larger than in other regions, indicating a greater temperature gradient change. Therefore... The larger the value, the greater the value.

[0092] Because blood flow within superficial arteries is relatively stable, their temperature variations are relatively small (i.e., small temperature variance); while the surrounding skin is affected by environmental factors (such as airflow and heat dissipation from the body surface), resulting in larger temperature fluctuations (i.e., large temperature variance). Using the sliding window algorithm to calculate the local temperature variance can further distinguish between the vascular region and the surrounding skin region. The specific calculation formula is as follows: ; in, This represents the local temperature variance. To preset the size of the sliding window, For the pixels within the preset sliding window relative to the target pixel offset coordinates, For pixels in the corrected temperature matrix The corresponding temperature value. The local temperature variance value reflects the degree of temperature fluctuation within the local area covered by the preset sliding window. The larger the variance, the more unstable the temperature change in that area. To balance local temperature stability analysis and regional coverage, it is necessary to ensure that the sliding window can cover a space larger than the array itself, capturing the continuous temperature distribution characteristics of blood vessels, and avoiding the segmentation of blood vessel areas due to array size limitations. For example, if a 4×4 infrared array sensor is selected, the settings should be... , This refers to a 5×5 sliding window. The preset sliding window is a pre-defined window that moves within the corrected temperature matrix; in this embodiment, the size of the preset sliding window is not limited.

[0093] The average temperature value within the preset sliding window can be calculated using the following formula: .

[0094] By calculating the temperature variance value of a specific region, i.e. This can reflect the The dispersion of temperature data within a preset sliding window centered on the core artery is considered. Superficial arteries, due to the continuous flow of blood at the core temperature, exhibit smaller temperature fluctuations. The values ​​are significantly low; while the surrounding skin is directly exposed to the environment and is affected by external temperature, airflow, etc., making the temperature prone to fluctuations, and the corresponding area The value is relatively high.

[0095] Combined temperature gradient value in a certain region The temperature gradient is greater than the preset temperature gradient threshold, and the temperature variance in this region is... When the variance is less than a preset variance threshold, the region can be identified as a superficial artery. In other words, if a region simultaneously meets both a "high gradient value" and a "low variance value," it can be more accurately identified as a superficial artery, thereby reducing the false positive rate of single-feature judgment. By analyzing the temperature gradient value and the region's temperature stability characteristic value, the potential vessel boundary location can be preliminarily determined. In this embodiment, the specific values ​​of the preset temperature gradient threshold and the preset variance threshold are not limited.

[0096] The preset temperature gradient threshold is a pre-defined critical value used to determine whether a temperature gradient value is significant. When the overall temperature gradient value exceeds this preset threshold, the temperature change at that location is considered relatively drastic, possibly near a blood vessel boundary, thus allowing the extraction of temperature gradient feature values. The preset variance threshold is a pre-defined critical value used to determine whether a local temperature variance value is significant. When the local temperature variance value exceeds this preset variance threshold, the temperature stability of that region is considered poor, possibly near a blood vessel boundary, thus allowing the extraction of regional temperature stability feature values.

[0097] (4) Then, after determining the potential vascular boundary location of the superficial artery measurement area of ​​the subject, the high temperature area is extracted from the potential vascular boundary location of the superficial artery measurement area of ​​the subject according to the adaptive threshold segmentation algorithm and the preset temperature difference value, thereby determining the target superficial artery vascular area.

[0098] Specifically, first calculate the corrected temperature matrix. arithmetic mean and standard deviation .

[0099] Arithmetic mean The average temperature value of all pixels in the corrected temperature matrix, reflecting the overall temperature central tendency, is calculated using the following formula: ; in, The array size of the infrared array sensor (e.g., when the infrared array sensor is a 4×4 array). n (Total number of pixels is 16). For the corrected temperature matrix, the first... line, number Temperature values ​​corresponding to the column pixels.

[0100] Standard deviation The formula used to measure the dispersion of temperature values ​​across all pixels in a temperature matrix, i.e., the uniformity of temperature distribution, is as follows: ; in, It is the arithmetic mean; The deviation of the temperature value of a single pixel from the arithmetic mean is represented by the square root of the summation, average, and then the overall temperature dispersion is obtained.

[0101] Then, through the formula: Calculate the dynamic temperature threshold Based on the experimental data, a threshold coefficient was set. ,generally The value ranges from 1.5 to 2. The standard deviation of the corrected temperature matrix. This reflects the degree of temperature dispersion in the superficial arterial region. In normal measurement scenarios, this standard deviation... The temperature is usually stable between 0.3℃ and 0.6℃; this data is based on statistical experimental data. At that time, the threshold offset is This corresponds to an actual temperature difference of approximately 0.45℃-0.9℃; when At that time, the threshold offset is This corresponds to an actual temperature difference of approximately 0.6℃-1.2℃. To ensure that the selected high-temperature areas include intact superficial arteries and meet the accuracy standard of medical-grade electronic thermometers in GB / T 21416-2008 "Medical Electronic Thermometers," with an error S ≤ 0.2℃, here... The value is 1.8, and the threshold offset is... This corresponds to an actual temperature difference of approximately 0.54℃-1.08℃. This avoids both the severing of blood vessels due to an excessively small threshold coefficient and the introduction of excessive skin interference due to an excessively large threshold coefficient. For example, experimental data shows that when... When the adaptive threshold segmentation is applied, the recognition accuracy of the superficial temporal artery region can reach over 98%, and it has the best compatibility with subsequent connected component analysis and peak tracking algorithms. Finally, the body temperature measurement error can be controlled within 0.2℃.

[0102] Finally, retain The selected areas are the target superficial arterial vessel regions. Due to interference from ambient temperature and individual differences among the subjects, the threshold coefficient... It will change with the real-time standard deviation. and ambient temperature Adaptive adjustment, or dynamic threshold adjustment, ensures that the device dynamically adjusts the threshold based on the real-time environment and individual characteristics during each measurement, thereby accurately identifying superficial arterial areas and providing a reliable basis for subsequent body temperature calculations.

[0103] (5) Finally, the corrected temperature matrix corresponding to the target superficial artery region is subjected to peak tracking processing to determine the peak temperature value of the target superficial artery region, and the peak temperature value of the target superficial artery region is used as the body temperature value of the subject. Among them, peak tracking processing involves searching for the highest temperature point within the target superficial artery region and tracking the position change of the highest point to determine the core temperature of the superficial artery, i.e., the peak temperature value. The core of peak tracking processing is to locate the vessel center through local feature analysis of the temperature curve, i.e., the area covered by continuous peak points. These peak points correspond to the highest temperature of the superficial artery center. After the previous noise reduction processing, data correction, feature extraction and adaptive threshold segmentation, the superficial artery region has been accurately located, and the vessel center temperature finally captured by peak tracking processing is the measurement result that can be used to characterize human body temperature.

[0104] Specifically, the corrected temperature matrix Along the horizontal direction (scanning direction, i.e., column direction) Expanding by row yields multiple one-dimensional temperature curves, namely: , ( ); in, This is the row index of the corrected temperature matrix (corresponding to different sensing elements of the sensor). This is the column index (horizontal scan position) of the corrected temperature matrix. For array size (such as in a 4×4 infrared array sensor) , For each one-dimensional temperature curve A three-point sliding window (i.e., coverage) is used. , , If the following conditions are met: ; ; ; ; Then determine This is the peak point of the one-dimensional temperature curve, with corresponding coordinates of... .

[0105] The above method outputs a set of coordinates for the trajectory of the blood vessel center. and the corresponding temperature value ,in, Peak point The corresponding temperature value, Peak point The corresponding temperature value, Peak point The corresponding temperature values. This set of coordinates for the vessel center trajectory reflects the continuous course of the superficial artery within the lateral scanning range. Finally, by weighting or averaging the temperature values ​​corresponding to the vessel center trajectory coordinates, the peak temperature value of the target superficial artery region can be determined. This peak temperature value represents the true temperature of the vessel center, i.e., the subject's body temperature.

[0106] It should be noted that in some examples, after obtaining the target superficial artery region, morphological operations can be used to perform connected component analysis on the binary matrix of the target superficial artery region to further determine the superficial artery region. Specifically, this includes: The binary matrix of the target superficial artery region is filled with gaps using the dilation operation formula, and isolated noise points in the binary matrix of the target superficial artery region are removed using the erosion operation formula, resulting in an optimized binary matrix. Calculate the area of ​​multiple connected regions in the optimized binary matrix, and determine the optimized superficial arterial vessel region from the multiple connected region areas based on preset pixel values.

[0107] Superficial arteries form continuous tubular structures beneath the human epidermis. Morphological operations are used to process the thresholded binary image to remove isolated high-temperature noise points, thus preserving the continuous vascular region. This stage mainly involves two morphological operations: dilation and erosion. These operations are based on a binary matrix (denoted as A, where "1" represents foreground pixels and "0" represents background pixels) and a structuring element (denoted as B; due to the selection of a 4×4 infrared array sensor, the structuring element is set to 3×3 here, which effectively fills the tiny gaps within the vascular region without excessively expanding the vascular boundary).

[0108] It should be noted that, in this embodiment, if the thermometer uses a 4×4 infrared array sensor, then the morphological operation in this embodiment uses a 3×3 square structuring element (element matrix is...). Where "1" represents the pixel area covered by the structuring element. The criteria for selecting a 3×3 square structuring element are as follows: (1) Matching the resolution of the infrared array sensor. The thermometer in this embodiment uses a 4×4 infrared array sensor. The detection range of a single sensing element is 2mm-3mm, and the overall measurement area is 8mm-12mm. The projection width of superficial arteries on the body surface is 5mm-8mm (such as the superficial temporal artery in the forehead). The actual spatial coverage of the 3×3 square structural element is 6mm-9mm (of which, the coverage of a single structural element pixel is 2mm-3mm). It can completely cover the cross-section of the blood vessel, avoiding the inability to fill the gap between blood vessels due to the structural element being too small (such as a 2×2 square structural element), or the excessive expansion of the blood vessel boundary due to the structural element being too large (such as a 4×4 square structural element), which would cause it to mix into the surrounding skin area.

[0109] (2) Balancing noise removal and vascular integrity. Experimental verification shows that when the structuring element size is less than 3×3 (e.g., 2×2), although it can remove tiny isolated noise points (diameter ≤ 2mm), it cannot fill the tiny gaps (e.g., width 1mm-2mm) in the vascular area caused by hair occlusion and skin folds, resulting in vascular area breakage. When the structuring element size is greater than 3×3 (e.g., 4×4), although it can fill the gaps, it will misjudge the 1mm-2mm skin area around the blood vessel as part of the blood vessel, resulting in distorted vascular area contour. The 3×3 square structuring element can achieve a balance between "removing isolated noise points with a diameter ≤ 3mm" and "filling vascular gaps with a width ≤ 2mm", ensuring that the optimized vascular area is both complete and free of redundant interference.

[0110] To verify the effectiveness of the 3×3 square structural element when the thermometer uses a 4×4 infrared array sensor, this embodiment selects 50 healthy subjects (aged 20-60 years, 25 males and 25 females) to perform measurements on the superficial temporal artery in the forehead and superficial carotid artery in the neck, comparing the optimization effects of different structural element sizes. Table 1 shows the optimization effects of structural elements of different sizes. As can be seen from Table 1, the 3×3 structural element exhibits the best overall performance in terms of "vascular region integrity," "noise removal rate," and "size deviation," meeting the thermometer's requirement for accurate positioning of the superficial artery region (deviation ≤ 0.2 mm). Therefore, when the thermometer uses a 4×4 infrared array sensor, the 3×3 square structural element is determined as the optimal structural element parameter.

[0111] Table 1. Optimization effect of structural elements of different sizes

[0112] Specifically, the formula for the expansion operation (filling gaps) is: ; in, Let be the pixel coordinates in binary matrix A, representing the position of any pixel in binary matrix A. For each pixel in binary matrix A, if there is at least one "1" in its neighborhood (defined by structuring element B), then the pixel is marked as "1". Dilation can fill small gaps within vascular regions, connecting discontinuous vascular segments into a complete region.

[0113] The formula for corrosion operation (deburring) is: ; For each pixel in the binary matrix A, if all pixels in its neighborhood (defined by the structuring element B) are "1", then the pixel is retained as "1"; otherwise, it is marked as "0". Erosion can remove isolated noise points (such as spurs) at the edges of vascular regions, thus optimizing vascular morphology.

[0114] In this embodiment, a dilation operation is performed once. This involves traversing a binary matrix (where "1" represents foreground pixels, i.e., the target blood vessel region, and "0" represents background pixels) using a 3×3 square structuring element. If at least one foreground pixel with a value of "1" exists within the structuring element's coverage area, the center pixel is marked as "1," thus filling the tiny gaps (i.e., gaps of one pixel) within the blood vessel region and connecting the broken blood vessel segments into a continuous region. In this embodiment, the dilation operation is limited to once. Performing it twice or more would cause the blood vessel region boundary to expand outward by more than 0.5 mm, increasing the deviation from the actual blood vessel size.

[0115] After the dilation operation, an erosion operation is performed. This involves traversing the dilated binary matrix using the same 3×3 square structuring element. Only when all pixels within the structuring element's coverage area are "1" are the center pixels retained as "1"; otherwise, they are marked as "0". This removes edge burrs introduced during the dilation operation (such as isolated noise points of one pixel around a blood vessel) and restores the true contour of the blood vessel. The number of erosion operations is kept consistent with the number of dilation operations, i.e., only one, to avoid excessive shrinkage of the blood vessel area due to too many erosion operations (shrinkage amplitude ≤ 0.3mm), ensuring that the core area of ​​the blood vessel is not lost.

[0116] After morphological processing involving "dilation and erosion," the output is an optimized binary matrix. Consecutive "1" regions represent the optimized superficial arterial vessel regions after filtering, while "0" regions represent the background (skin or noise). Simultaneously, by calculating the area of ​​connected components (counting the number of pixels in each consecutive "1" region), connected components with areas within a reasonable range (typically 5-30 pixels) are retained, while excessively large regions (potentially containing non-vascular tissue) or excessively small regions (potentially noise) are excluded. Figure 3 As shown, Figure 3 This is a schematic diagram illustrating the effect of morphological processing on a target superficial arterial vascular region before such processing, according to an embodiment of this application. Figure 4As shown, Figure 4 This is a schematic diagram illustrating the effect of morphological processing on a target superficial arterial vessel region according to an embodiment of this application. (Comparison is needed for a clearer understanding of the effect.) Figure 3 and Figure 4 As can be seen, after morphological processing, isolated noise points were removed, and the vascular morphology became more complete.

[0117] It should be noted that in this embodiment, connected component analysis may or may not be performed, depending on the actual situation.

[0118] It is understood that the thermometer provided in this application has the following advantages compared with existing non-contact infrared measuring instruments: (1) The infrared array sensor can accurately locate superficial arteries by collecting spatial temperature distribution, significantly improving the accuracy of temperature measurement and getting closer to the core body temperature. (2) The integrated ambient temperature sensor and dynamic compensation algorithm can solve the error problem in high and low temperature environments, while allowing slight hair and skin folds to cover the area. The multi-point data avoids the obstructed area and has strong anti-physical interference ability. (3) Through non-contact measurement, there is no need to touch the skin, avoiding cross-infection. It is suitable for densely populated scenes such as hospitals and kindergartens, and the non-invasive measurement makes it easy for the test subjects to accept. At the same time, the infrared array sensor has a large detection window coverage area, which can accurately identify the location of superficial arteries, greatly improving the ease of operation and making it suitable for a wider range of people. (4) The total time for multi-point data acquisition and algorithm processing is less than 2 seconds, and the body temperature value can be quickly measured without waiting for the body surface temperature to balance with the environment. The response speed is fast and the user's waiting time is reduced. (5) This thermometer does not require hazardous materials such as glass or mercury. The outer shell can be made of food-grade ABS plastic, which is drop-resistant and durable, making it suitable for families with children. The infrared array sensor and processing chip can be miniaturized and integrated, and the lens system can be replaced with metasurface materials (such as metalenses), greatly reducing the size of the device and balancing portability and functionality. At the same time, there is no exposed probe (the infrared sensing window is a sealed design), so it does not require frequent disinfection, is easy to maintain, and is suitable for high-frequency use scenarios such as medical places.

[0119] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this application, and not to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. These modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application, and should all be included within the protection scope of this application. In addition, those skilled in the art can understand that although some embodiments herein include certain features included in other embodiments but not other features, combinations of features from different embodiments are meant to be within the scope of this application and form different embodiments.

Claims

1. A temperature measuring instrument, characterized in that, include: The housing (10), infrared array sensor (20), ambient temperature sensor (30), controller (40) and display (50) are provided inside the housing (10); The infrared array sensor (20) is connected to the controller (40) and is used to collect infrared radiation signals from the superficial artery measurement area of ​​the subject, convert the infrared radiation signals into an initial temperature matrix, and send the initial temperature matrix to the controller (40). The ambient temperature sensor (30) is connected to the controller (40) and is used to collect the ambient temperature value of the environment where the subject is located and send the ambient temperature value to the controller (40); The controller (40) is connected to the display (50) and is used to receive the initial temperature matrix and the ambient temperature value, and to determine the body temperature value of the subject based on the initial temperature matrix and the ambient temperature value. The display (50) is disposed on the surface of the housing (10) for displaying the body temperature value.

2. The thermometer as described in claim 1, characterized in that, The housing (10) is provided with a probe (11) facing the superficial artery measurement area of ​​the subject.

3. The temperature measuring instrument as described in claim 2, characterized in that, The detection surface of the infrared array sensor (20) is parallel to the opening end face of the detection part (11), and the central axis of the detection surface of the infrared array sensor (20) coincides with the central axis of the opening end face of the detection part (11).

4. The temperature measuring instrument as described in claim 3, characterized in that, An infrared optical component is provided at the opening end face of the detection unit (11). The infrared optical component is used to focus the infrared radiation signal of the superficial artery measurement area of ​​the subject onto the detection surface of the infrared array sensor (20) so that the infrared array sensor (20) can collect the infrared radiation signal.

5. The temperature measuring instrument as described in claim 4, characterized in that, The infrared optical component is a superlens.

6. The temperature measuring instrument as described in claim 1, characterized in that, The grip portion (12) of the housing (10) is provided with an inwardly recessed groove with a horizontal bottom side.

7. The temperature measuring instrument as described in claim 6, characterized in that, The display (50) is disposed in the inner wall region of the groove.

8. The temperature measuring instrument according to any one of claims 1-7, characterized in that, A switch measurement button (60) is provided on the grip part (12) of the housing (10). The switch measurement button (60) is connected to the controller (40) and the power supply respectively, and is used to turn the thermometer (1) on or off.

9. The temperature measuring instrument as described in claim 8, characterized in that, The switch measurement button (60) is also used to send a measurement start signal to the controller (40).

10. The temperature measuring instrument as described in claim 2, characterized in that, The detection part (11) of the housing (10) is cylindrical.

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