US20200085414A1 - Bodily fluid collection devices and related methods - Google Patents
Bodily fluid collection devices and related methods Download PDFInfo
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- US20200085414A1 US20200085414A1 US16/571,028 US201916571028A US2020085414A1 US 20200085414 A1 US20200085414 A1 US 20200085414A1 US 201916571028 A US201916571028 A US 201916571028A US 2020085414 A1 US2020085414 A1 US 2020085414A1
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Definitions
- the present technology is related to collecting bodily fluid from a patient.
- various embodiments of the present technology are related to handheld bodily fluid collection devices and related methods.
- Devices, systems and methods to collect bodily fluids are widely used in personalized, clinical and field medical applications.
- Biological samples are commonly collected using simple lancing devices or more sophisticated devices that require trained personnel (e.g., phlebotomy venipunctures).
- Transferring bodily fluids to a container, receptacle or an analysis device often requires several steps, which can be time consuming, prone to error and/or cumbersome.
- many personalized devices designed for untrained users can obtain only very limited volumes of bodily fluid, which in turn limits the applicability of such devices.
- FIG. 1A is a perspective view of a bodily fluid collection device configured in accordance with an embodiment of the present technology.
- FIG. 1B is a perspective view of the bodily fluid collection device of FIG. 1A in use.
- FIG. 1C is a perspective view illustrating detachment of the collection reservoir from the bodily fluid collection device of FIG. 1A .
- FIG. 2A is a schematic cross-sectional illustration of a bodily fluid collection device configured in accordance with an embodiment of the present technology.
- FIG. 2B is a side view of a skin-piercing feature configured in accordance with the present technology.
- FIG. 2C is a side view of a skin-piercing feature with a stop feature configured in accordance with the present technology.
- FIG. 3 is a block diagram of a method for using a bodily fluid collection device in accordance with an embodiment of the present technology.
- FIG. 4 is a block diagram of a method for deploying a skin-piercing feature using an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology.
- FIGS. 5A-5C are schematic cross-sectional illustrations of the operation of an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology.
- FIG. 6A is a cross-sectional view of a bodily fluid collection device with an in situ loaded actuation mechanism configured in accordance with an embodiment of the present technology.
- FIG. 6B is a cross-sectional view of internal components of the device of FIG. 6A .
- FIG. 6C is a top view of internal components of the device of FIG. 6A .
- FIG. 6D is a perspective view of internal components of the device of FIG. 6A .
- FIG. 6E is an exploded view of internal components of the device of FIG. 6A .
- FIG. 7 is a cross-sectional view of the device of FIG. 6A in a deployment state.
- FIG. 8 is a cross-sectional view of the device of FIG. 6A in a peak deployment state.
- FIG. 9 is a cross-sectional view of the device of FIG. 6A in a retraction state.
- FIG. 10 is a cross-sectional view of the device of FIG. 6A in a re-actuation state.
- FIGS. 11A-11H are schematic top and cross-sectional illustrations of the operation of a pre-loaded actuation mechanism in accordance with the present technology.
- FIGS. 12A-12C are schematic cross-sectional illustrations of the operation of a locking mechanism configured in accordance with an embodiment of the present technology.
- FIGS. 13A-13D are schematic cross-sectional illustrations of a vacuum being applied to a patient's skin in accordance with an embodiment of the present technology.
- FIGS. 14A-14C are schematic cross-sectional illustrations of a vacuum being applied to a patient's a patient's skin in accordance with an embodiment of the present technology.
- FIGS. 15A-15C are schematic cross-sectional illustrations of the operation of a dynamically-generated vacuum mechanism in accordance with an embodiment of the present technology.
- FIGS. 16A-16C are schematic cross-sectional illustrations of the operation of another dynamically-generated vacuum mechanism in accordance with an embodiment of the present technology.
- FIGS. 17A and 17B are schematic cross-sectional illustrations of the operation of a dynamically-generated vacuum mechanism integrated into the skin-piercing assembly in accordance with an embodiment of the present technology.
- FIGS. 18A and 18B are cross-sectional views of a bodily fluid collection device having a dynamically-generated vacuum mechanism integrated into the skin-piercing assembly and configured in accordance with an embodiment of the present technology.
- FIGS. 19A-19E are schematic cross-sectional illustrations of skin interfaces to control skin curvature in accordance with embodiments of the present technology.
- FIG. 20 is a block diagram of a method for withdrawing bodily fluid from a patient's skin using a flexible membrane in accordance with an embodiment of the present technology.
- FIGS. 21A-21C are cross-sectional and perspective views of the flexible membrane of a bodily fluid collection device in accordance with an embodiment of the present technology.
- FIG. 22 is an exploded view of the flexible membrane configured in accordance with an embodiment of the present technology.
- FIGS. 23A-23E are various views of flexible membranes with different surface features and/or treatments configured in accordance with embodiments of the present technology.
- FIGS. 24A-24F are cross-sectional views of housing features to control flow of bodily fluid along the flexible membrane in accordance with embodiments of the present technology.
- FIGS. 25A-25F are cross-sectional and top views of a wicking element for directing flow of a bodily fluid in accordance with an embodiment of the present technology.
- Devices and methods in accordance with the present technology can be configured to deploy a skin-piercing feature toward a patient's skin to withdraw bodily fluid (e.g., blood).
- bodily fluid e.g., blood
- the devices and methods disclosed herein use an actuation mechanism that deploys the skin-piercing feature in response to movement of an actuator.
- the devices and methods disclosed herein use a vacuum mechanism configured to dynamically generate a vacuum that is applied to the patient's skin to facilitate collection of the bodily fluid.
- the devices and methods disclosed herein use a flexible membrane that interfaces with the patient's skin and/or bodily fluid for more efficient withdrawal of bodily fluid.
- the devices and methods of the present technology can be used to quickly and easily obtain a volume of bodily fluid sufficient for downstream testing and analysis.
- FIGS. 1A-25F Specific details of the present technology are described herein with reference to FIGS. 1A-25F . It should be noted that other embodiments in addition to those disclosed herein are within the scope of the present technology. Further, some embodiments of the present technology can have different configurations, components, and/or procedures than those shown or described herein. Moreover, a person of ordinary skill in the art will understand that some embodiments of the present technology can have configurations, components, and/or procedures in addition to those shown or described herein and that these and other embodiments can be without several of the configurations, components, and/or procedures shown or described herein without deviating from the present technology.
- FIG. 1A is a perspective view of a bodily fluid collection device 100 (“device 100 ”) configured in accordance with an embodiment of the present technology.
- the device 100 can be handheld with a size that is easily grasped and manipulated by one or both of a patient's hands.
- Such handheld devices advantageously allow a patient to collect a bodily fluid sample (e.g., a blood sample) without assistance from another individual.
- the handheld devices of the present technology can be operated by a layperson outside of a medical setting (e.g., at home or in a field clinic) and without aid of a medical professional.
- the device 100 includes a housing 102 and an actuator 104 .
- the actuator 104 e.g., a button
- the housing 102 is removably coupled to a collection reservoir 200 (e.g., a tube or cartridge) for receiving the bodily fluid withdrawn from the patient.
- the reservoir 200 can act as a removable and standardized container for bodily fluid that can be detached and inserted into clinical and laboratory equipment or workflows, e.g., for diagnostics and/or biomarker detection.
- FIG. 1B is a perspective view of the bodily fluid collection device 100 in use.
- the device 100 is applied to a patient's body, with the bottom surface of the housing 102 positioned against the skin 250 and the actuator 104 positioned away from the skin 250 .
- Pressing the actuator 104 deploys a skin-piercing feature (e.g., a lancet, blade, or needle) from within the device 100 to pierce the skin 250 .
- a skin-piercing feature e.g., a lancet, blade, or needle
- Subsequent retraction of the actuator 104 away from the skin creates a vacuum within the device 100 that acts against the patient's skin either directly or indirectly. Bodily fluid from the resulting incision is withdrawn into the housing 102 and collected into the reservoir 200 .
- FIG. 1C is a perspective view illustrating detachment of the collection reservoir 200 from the bodily fluid collection device 100 .
- FIG. 2A is a schematic cross-sectional illustration of a bodily fluid collection device 100 configured in accordance with an embodiment the present technology.
- the device 100 includes the housing 102 , the actuator 104 , a skin-piercing assembly 106 located at least partially or completely within the housing 102 , and an opening 108 through the housing 102 .
- the opening 108 is formed in a bottom surface 110 of the housing 102 such that the opening 108 is against the skin when the device 100 is applied to a patient's body.
- the actuator 104 is movable relative to the housing 102 along a deployment direction 112 and a retraction direction 114 .
- the deployment direction 112 can be a downward direction in the orientation of FIG.
- the retraction direction 114 can be an upward direction, e.g., away from the opening 108 .
- the deployment direction 112 is generally toward the skin, while the retraction direction 114 is generally away from the skin.
- the skin-piercing assembly 106 includes at least one skin-piercing feature 116 (e.g., a lancet, blade, or needle) and a biasing member 118 (e.g., a spring) that is coupled to the skin-piercing feature 116 .
- the biasing member 118 is configured to drive the skin-piercing feature 116 along the deployment direction 112 toward the opening 108 .
- the skin-piercing feature 116 can be configured to pierce the patient's skin to create an incision from which bodily fluid can be withdrawn.
- the size of the skin-piercing feature can be varied as desired. For example, a relatively large skin-piercing feature can be advantageous for creating a larger incision that allows for withdrawal of larger volumes of bodily fluid.
- the skin-piercing assembly 106 can include a plurality of skin-piercing features, e.g., two, three, four, five, or more skin-piercing features.
- the device 100 can include a corresponding number of openings 108 , such that each skin-piercing feature passes through a respective opening to pierce the patient's skin.
- more than one skin piercing feature 116 can pass through an opening 108 .
- all of the skin piercing features 116 can pass through a single opening 108 .
- FIG. 2B is a side view of the skin-piercing feature 116 of the device 100 configured in accordance with an embodiment the present technology.
- the length of the skin-piercing feature 116 can be selected to produce an appropriate penetration depth into the skin 250 .
- the skin-piercing feature 116 can have a length of about 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, 3.5 mm, 3.6 mm, 3.7 mm, 3.8 mm, 3.9 mm, or
- the length of the skin-piercing feature 116 can be selected to produce a penetration depth less than or equal to about 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, 3.5 mm, 3.6 mm, 3.7 mm, 3.8 mm, 3.9 mm, or 4.0 mm below the surface of the skin 250 .
- FIG. 2C is a side view of the skin-piercing feature 116 with a stop feature 117 configured in accordance with an embodiment the present technology.
- the stop feature 117 is at or near the base of the skin-piercing feature 116 to limit the penetration depth of the skin-piercing feature 116 into the skin.
- the stop feature 117 can limit the penetration depth to less than or equal to about 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, 3.5 mm, 3.6 mm, 3.7 mm, 3.8 mm, 3.9 mm, or 4.0 mm below the surface of the skin 250 .
- the device 100 includes an actuation mechanism for actuating the deployment of the skin-piercing assembly 106 .
- the actuator 104 can be mechanically coupled to the skin-piercing assembly 106 , e.g., via a platform 120 and a plunger 122 , to deploy the skin-piercing feature along the deployment direction 112 .
- the platform 120 is located at least partially within the actuator 104
- the plunger 122 is located at least partially within the platform 120
- the skin-piercing assembly 106 is coupled to the plunger 122 .
- the actuation mechanism can also actuate the retraction of the skin-piercing feature 116 along the retraction direction 114 , after the skin-piercing feature 116 has been deployed. Additional features and implementations of the actuation mechanism are described herein with reference to FIGS. 4-12C .
- the device 100 includes a vacuum mechanism to facilitate collection of the bodily fluid.
- the device 100 can include a sealing member 124 (e.g., a flexible membrane that can bend and/or is elastic) over the opening 108 to form a lumen 126 .
- the device 100 can include at least one valve 128 fluidically connected to the lumen 126 to control air flow into and out of the lumen 126 .
- the sealing member 124 can be mechanically coupled to the skin-piercing assembly 106 , e.g., via the plunger 122 , such that movement of the skin-piercing assembly 106 along the deployment direction 112 decreases the volume of the lumen 126 , and movement of the skin-piercing assembly 106 along the retraction direction 114 increases the volume of the lumen 126 .
- the valve 128 can be a one-way valve that permits air to escape from within the lumen 126 , e.g., as the lumen volume decreases, but prevents air from entering the lumen 126 , e.g., as the lumen volume increases. This creates a low-pressure region (e.g., a vacuum) within the lumen 126 that acts directly or indirectly against the skin. Additional features and implementations of the vacuum mechanism are described herein with reference to FIGS. 13A-18B .
- the device 100 includes a skin interface that interacts with the patient's skin and/or bodily fluid to facilitate collection of the bodily fluid.
- the skin interface can control the curvature of the skin to maintain the incision in an open position, thus promoting flow of the bodily fluid from the skin.
- the skin interface can also include surface features and/or treatments to direct flow of the bodily fluid toward a desired location, e.g., into the housing 102 and toward the collection reservoir.
- the device 100 can include a flexible membrane 130 coupled to the housing 102 and covering at least a portion of the opening 108 .
- the flexible membrane 130 can be bendable and/or stretchable (e.g., elastic).
- the flexible membrane 130 can be coupled to the bottom surface 110 of the housing 102 , such that the membrane 130 is on the exterior of the housing 102 . Alternatively, the flexible membrane 130 can be within the interior of the housing 102 .
- the flexible membrane 130 can optionally include an aperture to allow the skin-piercing feature 116 to pass through.
- the flexible membrane 130 can be made of an elastic material (e.g., polyurethane, silicone) that deforms into a curved shape when exposed to a vacuum. When the device 100 is applied to the patient's body, the flexible membrane 130 can form a seal against the patient's skin to control the skin curvature and/or direct flow of the bodily fluid from the skin. Additional features and implementations of skin interfaces are described herein with reference to FIGS. 19A-25F .
- FIG. 3 is a block diagram of a method 300 for using a bodily fluid collection device configured in accordance with an embodiment the present technology. Although various steps of the method 300 are described with respect to the components of the device 100 , it shall be appreciated that the method 300 is generally applicable to any embodiment of the bodily fluid collection devices disclosed herein.
- the method 300 includes providing a bodily fluid collection device having a skin-piercing feature (block 310 ) and deploying the skin-piercing feature toward a patient's skin (block 320 ).
- the deployment of the skin-piercing feature can be driven by an actuation mechanism, as described herein with reference to FIGS. 4-12C .
- the actuation mechanism includes an actuator mechanically coupled to the skin-piercing assembly, such that movement of the actuator along the deployment direction drives the skin-piercing feature to be deployed toward the opening along the deployment direction. For example, in the embodiment of FIG.
- the actuator 104 engages and moves the platform 120 along the deployment direction 112
- the platform 120 engages and moves the plunger 122 along the deployment direction 112
- the movement of the plunger 122 along the deployment direction 112 causes the skin-piercing feature 116 to be deployed.
- the movement of the plunger 122 along the deployment direction 112 releases a load on the biasing member 118 , thus causing the biasing member 118 to actively drive the skin-piercing feature 116 along the deployment direction 112 .
- the biasing member 118 is not initially loaded, but movement of the actuator 104 , platform 120 , and plunger 122 loads the biasing member 118 with a stored energy until the actuator reaches a trigger point that releases the skin-piercing feature 116 .
- This allows the stored energy in the biasing member 118 to be quickly released and thereby drive the skin-piercing feature 116 at a high velocity into the skin. This approach is expected to allow for easier device assembly, improve device stability and safety, increase device shelf life, and reduce fatigue on the biasing member.
- the skin-piercing feature can be deployed at any velocity suitable for creating an incision in the patient's skin for withdrawing bodily fluid.
- velocity may refer to a maximum velocity, an average velocity, or a velocity at the time the skin-piercing feature contacts the skin.
- the skin-piercing feature is deployed at a velocity greater than or equal to about 0.1 m/s, 0.2 m/s, 0.3 m/s, 0.4 m/s, 0.5 m/s, 0.6 m/s, 0.7 m/s, 0.8 m/s, 0.9 m/s, 1.0 m/s, 1.5 m/s, 2.0 m/s, or 2.5 m/s.
- the skin-piercing feature is deployed at a velocity less than or equal to about 0.1 m/s, 0.2 m/s, 0.3 m/s, 0.4 m/s, 0.5 m/s, 0.6 m/s, 0.7 m/s, 0.8 m/s, 0.9 m/s, 1.0 m/s, 1.5 m/s, 2.0 m/s, or 2.5 m/s. In some embodiments, the skin-piercing feature is deployed at a velocity within a range from about 0.1 m/s to about 2.5 m/s.
- the skin-piercing feature is deployed at a high velocity, e.g., a velocity greater than or equal to about 2.5 m/s.
- High velocity deployment of the skin-piercing feature can produce more effective penetration for some skin types with low stiffness or elasticity, create a larger incision that permits withdrawal of a larger volume of bodily fluid, or allow the use of the device on other mammalian species other than humans.
- the skin-piercing feature is deployed at a low velocity, e.g., a velocity less than or equal to about 0.1 m/s. Low velocity deployment of the skin-piercing feature can reduce the pain experienced by the patient.
- the method 300 further includes retracting the skin-piercing feature away from the patient's skin (block 330 ).
- the skin-piercing feature can be retracted by an actuation mechanism, as described herein with reference to FIGS. 4-12C .
- the skin-piercing feature can be retracted at least partially or completely into the housing along the retraction direction.
- the skin-piercing feature is retracted automatically after deployment such that the patient does not need to perform any additional actions for retraction to occur.
- the skin-piercing feature is locked into the retracted position such that further movement of the actuator along the deployment direction does not re-deploy the skin-piercing feature.
- the method 300 further includes applying a vacuum to the patient's skin (block 340 ).
- the device can include a vacuum mechanism that generates the vacuum contemporaneously with the deployment and retraction of the skin-piercing feature, as described herein with reference to FIGS. 13A-18B .
- a vacuum mechanism that generates the vacuum contemporaneously with the deployment and retraction of the skin-piercing feature, as described herein with reference to FIGS. 13A-18B .
- FIG. 2 movement of the plunger 122 along the deployment direction 112 decreases the volume of the lumen 126 . Air can escape from within the lumen 126 via the valve 128 as the volume decreases.
- the plunger 122 is moved along the retraction direction 114 , the volume of the lumen 126 increases, while the valve 128 prevents air from entering the lumen 126 .
- the pressure within the lumen 126 decreases, creating a vacuum within the lumen 126 that draws the bodily fluid and/or a portion of the patient's skin through the opening 108 .
- the valve can be mechanically shutoff as the plunger 122 reaches desired displacement position, such as the further-most displacement position. This is expected to increase the amount of bodily fluid withdrawn from the skin by opening local capillaries and maintaining the incision in an open configuration.
- the method 300 further includes withdrawing bodily fluid into the bodily fluid collection device (block 350 ).
- the skin-piercing feature has formed an incision in the patient's skin
- bodily fluid from the incision is drawn into the housing through the opening and into a collection reservoir.
- the device can include a skin interface (e.g., a flexible membrane) that interacts with the skin and/or bodily fluid to enhance flow of the bodily fluid into the device, as described herein with reference to FIGS. 19A-25F .
- a flexible membrane is expected to provide improved control over larger areas of skin, thus allowing the device to access more capillaries and increase the volume of bodily fluid that can be withdrawn, as well as provide a support to collect blood close to the incision point to prevent or at least mitigate the blood from travelling on the skin of the user. This further allows the delivery of anticoagulant material rapidly after the blood is extracted from the capillaries.
- draw volume can refer to the maximum volume of bodily fluid that can be collected from a specified percentage of the patient population, e.g., from at least 90% of patients.
- the draw volume of the device can be at least about 50 ⁇ L, 75 ⁇ L, 100 ⁇ L, 125 ⁇ L, 150 ⁇ L, 175 ⁇ L, 200 ⁇ L, 225 ⁇ L, 250 ⁇ L, 275 ⁇ L, 300 ⁇ L, 325 ⁇ L, 350 ⁇ L, 375 ⁇ L, 400 ⁇ L, 425 ⁇ L, 450 ⁇ L, 475 ⁇ L, 500 ⁇ L, 550 ⁇ L, 600 ⁇ L, 650 ⁇ L, 700 ⁇ L, 750 ⁇ L, 800 ⁇ L, 850 ⁇ L, 900 ⁇ L, 950 ⁇ L, 1 mL, 1.5 mL, or 2 mL of the bodily fluid from the patient.
- the draw volume of the device is up to about 50 ⁇ L, 75 ⁇ L, 100 ⁇ L, 125 ⁇ L, 150 ⁇ L, 175 ⁇ L, 200 ⁇ L, 225 ⁇ L, 250 ⁇ L, 275 ⁇ L, 300 ⁇ L, 325 ⁇ L, 350 ⁇ L, 375 ⁇ L, 400 ⁇ L, 425 ⁇ L, 450 ⁇ L, 475 ⁇ L, 500 ⁇ L, 550 ⁇ L, 600 ⁇ L, 650 ⁇ L, 700 ⁇ L, 750 ⁇ L, 800 ⁇ L, 850 ⁇ L, 900 ⁇ L, 950 ⁇ L, 1 mL, 1.5 mL, or 2 mL of the bodily fluid from the patient.
- the draw volume of the device is within a range from about 50 ⁇ L to about 2 mL, from about 100 ⁇ L to about 2 mL, from about 100 ⁇ L to about 1.5 mL, from about 100 ⁇ L to about 1 mL, or from about 100 ⁇ L to about 500 ⁇ L.
- the bodily fluid collection devices of the present technology can include an actuation mechanism that deploys the skin-piercing assembly.
- the actuation mechanism includes an actuator that is mechanically coupled to the skin-piercing assembly, such that movement of the actuator causes a skin-piercing feature of the skin-piercing assembly to be deployed along a deployment direction toward the patient's skin.
- the actuator movement that deploys the skin-piercing feature can be a simple, unidirectional movement that is easily performed by a layperson, such as pressing a button.
- the actuation mechanism can include a biasing member (e.g., a spring) that is coupled to the skin-piercing feature to drive the skin-piercing feature along a deployment direction.
- the biasing member can have an unloaded state (e.g., an uncompressed state), in which little or no load is placed on the biasing member (e.g., little or no energy is stored in the biasing member), and a loaded state (e.g., a compressed state), in which a load is placed on the biasing member (e.g., sufficient energy to drive the skin-piercing feature 116 at a desired velocity is stored in the biasing member).
- the biasing member transitions from the loaded state to the unloaded state, and the transition of the biasing member to the unloaded state drives the deployment of the skin-piercing feature in the deployment direction.
- the actuation mechanism is configured such that moving the actuator along the deployment direction both applies and releases a load on the biasing member (“in situ loaded”).
- An in situ loaded actuation mechanism may include little or no load on the biasing member before moving the actuator from an initial position along the deployment direction.
- the load on the biasing member before moving the actuator can be less than or equal to about 15%, 10%, 5%, or 1% of the maximum load on the biasing member during operation of the bodily fluid collection device.
- the length of the biasing member before moving the actuator from the initial position can be at least about 85%, 90%, 95%, or 99% of its unloaded length.
- Advantages of an in situ loaded actuation mechanism include easier device assembly, improved device stability and safety, longer device shelf life, and reduced fatigue on the biasing member.
- FIG. 4 is a block diagram of a method 400 for deploying a skin-piercing feature using an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology.
- the method 400 can be applied to any of the bodily fluid collection devices disclosed herein, such as the device 100 . Additionally, one or more steps of the method 400 can be combined with or substituted for any of the steps of the other methods disclosed herein. For example, one or more steps of the method 400 can be performed in combination with or as sub-steps of block 320 of the method 300 .
- the method 400 includes moving an actuator to a predetermined position (block 410 ).
- the predetermined position can be a position along a deployment direction (e.g., toward the patient's skin). For example, a patient can press the actuator once the bodily fluid collection device has been applied to the skin.
- the predetermined position is at least about 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 4.5 mm, 5 mm, 5.5 mm, 6 mm, 6.5 mm, 7 mm, 7.5 mm, 8 mm, 8.5 mm, 9 mm, 9.5 mm, 10 mm, 15 mm, or 20 mm from an initial resting position of the actuator.
- the method further includes applying a load to a biasing member coupled to a skin-piercing feature (block 420 ).
- the load can be applied to the biasing member by the movement of the actuator along the deployment direction to the predetermined position.
- the biasing member can initially be in an unloaded state with little or no applied load, and moving the actuator can increase the load on the biasing member to at least a partially loaded state, or to a fully loaded state.
- the actuator is mechanically coupled to the biasing member to apply the load on the biasing member, e.g., by compressing the biasing member.
- the biasing member can be compressed to a loaded length that is less than or equal to about 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, or 85% of its unloaded length.
- the method next includes moving the actuator beyond the predetermined position (block 430 ).
- the actuator can be moved to a position that is further along the deployment direction than the predetermined position, e.g., by the patient continuing to press on the actuator while the device is applied to the skin.
- the actuator is moved beyond the predetermined position by a distance of at least about 0.1 mm, 0.5 mm, 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 4.5 mm, or 5 mm.
- the method also includes releasing the load on the biasing member (block 440 ).
- the load can be released by moving the actuator along the deployment direction beyond the predetermined position.
- the method further includes driving the skin-piercing feature toward a patient's skin (block 450 ).
- the skin-piercing feature can be collectively driven toward the patient's skin by both the actuator and the biasing member.
- moving the actuator along the deployment direction beyond the predetermined position releases the load on the biasing member so that the biasing member actively drives the skin-piercing feature along the deployment direction.
- the biasing member can drive the skin-piercing feature as the biasing member extends from a compressed state toward an uncompressed state.
- FIGS. 5A-5C are schematic cross-sectional illustrations of the operation of an in situ loaded actuation mechanism 500 configured in accordance with an embodiment the present technology.
- the actuation mechanism 500 includes the biasing member 118 , the plunger 122 , the housing 102 , and the actuator (not shown).
- the skin-piercing feature 116 is coupled to the biasing member 118 via a base 502 .
- the plunger 122 is positioned around at least a portion of the skin-piercing assembly 106 and includes one or more projections 504 .
- the housing 102 includes the opening 108 and one or more arms 506 within the housing 102 .
- the actuator Before moving the actuator along the deployment direction ( FIG. 5A ), there is little or no loading on the biasing member 118 , such that the biasing member is at or near its uncompressed length.
- Moving the actuator along the deployment direction up to a predetermined position causes the arm(s) 506 to assume a flexed configuration that engages the base 502 and applies a load to the biasing member 118 .
- the actuator engages and moves the plunger 122 and skin-piercing assembly 106 downward toward the opening 108 . This downward movement brings the arm(s) 506 into engagement with the base 502 .
- the arm(s) 506 are in a flexed configuration (e.g., inwardly bent configuration) that presses up against the base 502 , causing the biasing member 118 to be compressed between the base 502 and the plunger 122 .
- Moving the actuator along the deployment direction beyond the predetermined position causes the arm(s) 506 to flex outward and thereby disengaged from the base 502 (e.g., a resting configuration or release configuration), which in turn releases the load on the biasing member 118 .
- the base 502 e.g., a resting configuration or release configuration
- continued downward movement of the actuator brings the projection(s) 504 of the plunger 122 into contact with the inwardly flexed arm(s) 506 .
- Each projection 504 contacts and displaces a corresponding arm 506 from the inwardly flexed configuration to a released configuration, e.g., by bending the arm 506 outward.
- the arm(s) 506 disengage from the base 502 and release the compression on the biasing member 118 .
- the biasing member 118 reverts toward its uncompressed length, driving the skin-piercing feature 116 downward toward the opening 108 .
- FIGS. 5A-5C illustrate a mechanism 500 with two projections and two arms
- alternative embodiments may include any suitable number of projections and arms.
- the mechanism 500 can include one, two, three, four, five, or more projections; and one, two, three, four, five, or more arms.
- the positioning of the projection(s) 504 and the arm(s) 506 can also be varied.
- the projection(s) 504 can be on the housing 102
- the arm(s) 506 can be on the plunger 122 .
- 5A-5C illustrate the arm(s) 506 being displaced outward by the projection(s) 504 to release the biasing member 118
- the arm(s) 506 may be displaced inward by the projection(s) 504 to release the biasing member 118 .
- FIGS. 6A-10 illustrate a bodily fluid collection device 100 with an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology.
- the device 100 includes the housing 102 , the actuator 104 , and the skin-piercing assembly 106 .
- the housing 102 includes an upper housing portion 602 A and a lower housing portion 602 B.
- the upper housing portion 602 A and the lower housing portion 602 B are separate components that are coupled together to form the housing 102 .
- the upper housing portion 602 A and lower housing portion 602 B can be integrally formed as a single unitary component.
- the upper housing portion 602 A is shaped to receive the actuator 104 .
- the lower housing portion 602 B includes the bottom surface 110 having the opening 108 .
- the actuator 104 is at least partially within the upper housing portion 602 A of the device 100 .
- the actuator 104 is a hollow, button-like structure positioned to be depressed by the patient along the deployment direction 112 to deploy the skin-piercing feature 116 of the skin-piercing assembly 106 .
- the actuator 104 can be mechanically coupled to the skin-piercing assembly 106 via one or more internal device components, such as the platform 120 , washer 604 , sealing member 124 , and/or plunger 122 .
- the actuator 104 is positioned around at least a portion of the platform 120 , the platform 120 is positioned around at least a portion of the washer 604 , and the washer 604 is positioned around at least a portion of the sealing member 124 , and the sealing member 124 is positioned around at least a portion of the plunger 122 .
- the actuator 104 , platform 120 , washer 604 , sealing member 124 , and plunger 122 can be concentrically positioned, such that the longitudinal axes (e.g., the axis extending along the deployment direction 112 ) of these components are aligned.
- the actuator 104 , platform 120 , washer 604 , sealing member 124 , and plunger 122 can be coupled to each other using any suitable combination of complementary interconnecting features (e.g., notches, grooves, projections, tabs, and the like).
- the lower edge 606 of the actuator 104 engages at least one tab feature 608 of the platform 120 when the actuator 104 is moved along the deployment direction 112 .
- the at least one tab feature 608 can extend radially outward from an outer surface of the platform 120 to receive and engage the lower edge 606 of the actuator 104 .
- the platform 120 includes at least one projecting feature 610 that engages at least one tab feature 612 of the washer 604 when the platform 120 is moved along the deployment direction 112 .
- the at least one projecting feature 610 can extend radially inward from an inner surface of the platform 120
- the at least one tab feature 612 can extend radially outward from an outer surface of the washer 604
- the washer 604 can include three tab features evenly spaced along the outer surface of the washer 604 , as shown in FIGS. 6C-6D .
- the lower edge 614 of the washer 604 engages the sealing member 124 and a collar feature 616 of the plunger 122 when the washer 604 is moved along the deployment direction 112 .
- the collar feature 616 can extend radially outward from an outer surface of the plunger 122 to receive and engage the lower edge 614 of the washer 604 .
- the actuator 104 , platform 120 , washer 604 , sealing member 124 , and plunger 122 are depicted in FIGS. 6A-6E as being separate components, one or more of these components may also be integrally formed with each other.
- the sealing member 124 and the plunger 122 can be integrally formed as a single unitary component, e.g., by overmolding.
- the washer 604 , sealing member 124 , and plunger 122 can be integrally formed as a single unitary component, e.g., by overmolding. Such approaches may be beneficial for reducing the number of components to simplify device assembly.
- the skin-piercing assembly 106 is mechanically coupled to the plunger 122 .
- the skin-piercing assembly 106 is coupled to an interior surface of the plunger 122 , such that the plunger 122 is around at least a portion of the skin-piercing assembly.
- the skin-piercing assembly 106 can include the biasing member 118 , base 502 , and at least one skin-piercing feature 116 .
- the biasing member 118 can have an upper portion coupled to the interior surface of the plunger 122 and a lower portion coupled to the base 502 .
- the skin-piercing feature 116 can be mounted to the base 502 .
- the device 100 includes at least one arm 506 within the housing 102 near the opening 108 .
- the arm 506 can be integrally formed with the lower housing portion 502 B, or can be a separate component that is coupled to the lower housing portion 502 B.
- the arm 506 can be a flexible component that is movable between a flexed configuration (e.g., an inwardly bent configuration) and a resting configuration (e.g., a straightened or outwardly bent configuration).
- FIG. 6A is a cross-sectional view of the device 100 prior to movement of the actuator 104 along the deployment direction 112 (“pre-actuation state”).
- pre-actuation state the arm 506 is initially in a flexed configuration engaging the base 502 .
- the base 502 can include a hook feature 618 that receives the end portion 620 of the arm 506 .
- the hook feature 618 can restrain the arm 506 in the flexed configuration and prevent the arm 506 from reverting to the released configuration.
- the actuator 104 When the actuator 104 is moved along the deployment direction 112 up to a predetermined position (“actuation state”), the platform, 120 , washer 604 , sealing member 124 , and plunger 122 are also moved along the deployment direction 112 by engagement of their respective interconnecting features, as discussed above. Accordingly, the arm 506 compresses the biasing member 118 between the base 502 and the plunger 122 , thus applying a load to the biasing member 118 .
- FIG. 7 is a cross-sectional view of the device 100 when the actuator 104 is moved beyond the predetermined position (“deployment state”)
- FIG. 8 is a cross-sectional view of the device 100 when the actuator 104 is at the maximum position along the deployment direction 112 (“peak deployment state”).
- the plunger 122 moves toward the arm 506 until the end portion 620 of the arm 506 contacts at least one projection 504 within the plunger 122 .
- the base 502 can include a notch formed in the hook feature 618 to permit contact between the end portion 620 of the arm 506 and the projection 504 .
- the projection 504 includes an inclined surface 622 that contacts and displaces the arm 506 outward from the hook feature 618 so that the arm 506 moves from the flexed configuration to the released configuration.
- the arm 506 disengages from the base 502 and deflects outward into a channel 624 formed between the projection 504 and a sidewall 626 of the plunger 122 .
- the plunger 122 can optionally include a latch portion 628 to restrict the movement of the skin-piercing feature 116 along the deployment direction 112 .
- the latch portion engages a complementary stop feature 630 on the base 502 to stop the movement of the base 502 and skin-piercing feature 116 along the deployment direction 112 .
- the latch portion 628 can be positioned away from the upper portion 632 of the plunger 122 , with the distance from the upper portion 632 and the latch portion 628 being configured to permit the skin-piercing feature 116 to attain a desired penetration velocity.
- the distance can be at least about 1 mm, 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, or 10 mm. In some embodiments, the distance can be within a range from about 4 mm to about 8 mm.
- FIG. 9 is a cross-sectional view of the device 100 after retraction of the skin-piercing feature 116 (“retraction state”).
- the actuation mechanism of the device 100 also automatically retracts the skin-piercing feature 116 after deployment without requiring any additional actuation of the device components by the patient.
- the device 100 can include a second biasing member 634 (e.g., a spring) configured to bias the skin-piercing feature 116 along the retraction direction 114 away from the opening 108 .
- a second biasing member 634 e.g., a spring
- the second biasing member 634 can have an unloaded state (e.g., an uncompressed state) in which little or no load is placed on the second biasing member 634 , and a loaded state (e.g., a compressed state) in which a load is placed on the second biasing member 634 .
- an unloaded state e.g., an uncompressed state
- a loaded state e.g., a compressed state
- the second biasing member 634 moves from the loaded state toward the unloaded state, and the movement of the second biasing member 634 toward the unloaded state drives the retraction of the skin-piercing feature 116 .
- the second biasing member can be coupled between the actuator 104 and the lower housing portion 602 B. As shown in FIGS. 7 and 8 , movement of the actuator 104 along the deployment direction compresses the second biasing member 634 , thus applying a load to the second biasing member 634 causing energy to be stored in the second biasing member 634 . When the patient or user stops pushing on the actuator 104 , the load on the second biasing member 634 is released, causing the second biasing member 634 to drive the actuator 104 along the retraction direction 114 .
- Movement of the actuator 104 along the retraction direction 114 also moves the platform 120 , washer 604 , sealing member 124 , and plunger 122 along the retraction direction 114 by engagement of their respective interconnecting features, as discussed above. Movement of the plunger 122 along the retraction direction 114 also retracts the biasing member 118 , base 502 , and skin-piercing feature 116 along the retraction direction 114 away from the opening 108 .
- the volume within the sealing member 124 increases causing a decrease in pressure (e.g., a vacuum) within the volume bounded by the sealing member 124 that draws blood from the patient.
- a decrease in pressure e.g., a vacuum
- FIG. 10 is a cross-sectional view of the device 100 when the actuator 104 is moved along the deployment direction 112 after retraction of the skin-piercing feature 116 (“re-actuation state”).
- the device 100 can include a locking mechanism configured to prevent re-deployment of the skin-piercing feature 116 after the skin-piercing feature 116 has already been retracted. Accordingly, even if the patient presses the actuator 104 again, the skin-piercing feature 116 is retained within the housing 102 and does not deploy. Additional features and implementations of the locking mechanism are described herein with reference to FIGS. 12A-12C .
- the bodily fluid collection devices of the present technology include an actuation mechanism in which the biasing member driving the deployment of the skin-piercing features is partially or fully loaded prior to movement of the actuator (“pre-loaded”). Accordingly, movement of the actuator along the deployment direction simply releases the load on the biasing member, with little or no additional loading applied.
- FIGS. 11A-11H are schematic top and cross-sectional illustrations of the operation of a pre-loaded actuation mechanism configured in accordance with an embodiment the present technology.
- the actuation mechanism includes a deployment assembly 1100 ( FIGS. 11A-11D ) and a retraction assembly 1150 ( FIGS. 11E-11G ).
- the deployment assembly 1100 includes a plate 1102 , an aperture 1104 in the plate 1102 , and a shaft 1106 extending through the aperture 1104 .
- the shaft 1106 includes an upper end portion 1108 A and a lower end portion 1108 B.
- the upper end portion 1108 A is coupled to at least one stop feature 1110 having a shape complementary to the shape of the aperture 1104 .
- the stop feature 1110 can include one or more tabs protruding radially outward from the shaft 1106
- the aperture 1104 can include one or more recesses shaped to receive the one more tabs.
- the lower end portion 1108 B is coupled to the base 502 carrying the skin-piercing feature 116 .
- the biasing member 118 is positioned at least partially around the shaft 1106 between the lower surface of the plate 1102 and the upper surface of the base 502 .
- the stop feature 1110 prior to actuation of the bodily fluid collection device, is oriented on the upper surface of the plate 1102 such that the stop feature 1110 is not aligned with the aperture 1104 .
- the stop feature 1110 can be rotated relative to the aperture 1104 such that the protrusions of the stop feature 1110 are not over the corresponding recesses of the aperture 1104 , and are instead against the upper surface of the plate 1102 . Accordingly, the stop feature 1110 prevents movement of the shaft 1106 , base 502 , and skin-piercing feature 116 toward the deployment direction.
- the length of the shaft 1106 can be selected such that the biasing member 118 is held between the base 502 and plate 1102 in at least a partially loaded state.
- the biasing member 118 can be held at a loaded length that is less than or equal to about 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, or 85% of its unloaded length.
- movement of the actuator along the deployment direction causes a rotational movement of the stop feature 1110 , e.g., along a rotational direction 1112 .
- the rotational direction 1112 can be a clockwise direction or a counterclockwise direction.
- the rotational movement brings the stop feature 1110 into alignment with the aperture 1104 such that the stop feature 1110 can pass through the aperture 1104 .
- the stop feature 1110 can be rotated such that the protrusions of the stop feature 1110 are over the corresponding recesses of the aperture 1104 .
- the alignment of the stop feature 1110 with the aperture 1104 releases the load on the biasing member 118 . Without the stop feature 1110 restraining the biasing member 118 to its loaded length, the biasing member 118 can extend toward its unloaded length, thus driving the base 502 and skin-piercing feature 116 along the deployment direction 112 toward the patient's skin.
- the retraction assembly 1150 can be used in combination with the deployment assembly 1100 to retract the skin-piercing feature 116 after deployment.
- the retraction assembly 1150 can be around at least a portion of the deployment assembly 1100 and/or the skin-piercing feature 116 .
- the retraction assembly 1150 includes a cap 1152 having an outer surface 1154 A and an inner surface 1154 B.
- the cap 1152 includes one or more protrusions 1156 extending radially outward from the outer surface 1154 A.
- the second biasing member 634 is received within a groove 1158 formed in the inner surface 1154 B of the cap 1152 .
- the second biasing member 634 is coupled between an inner collar 1160 of the cap 1152 and the housing 102 of the device.
- the retraction assembly 1150 further includes one or more latch features 1162 extending radially inward toward the cap 1152 .
- the latch features 1162 can be on a portion of the device that is stationary relative to the skin-piercing feature 116 , such as the housing 102 .
- the cap 1152 prior to deployment of the skin-piercing feature 116 , the cap 1152 can be oriented such that the protrusions 1156 are aligned with the latch features 1162 .
- the latch features 1162 can engage the protrusions 1156 such that the cap 1152 is held in place relative to the housing 102 .
- the height of the groove 1158 within the cap 1152 can be selected such that the second biasing member 634 is held between the inner collar 1160 and the housing 102 in at least a partially loaded state.
- the second biasing member 634 can be held at a loaded length that is less than or equal to about 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, or 85% of its unloaded length.
- the deployment of the skin-piercing feature causes a rotational movement of the cap 1152 , e.g., along a rotational direction 1164 .
- the rotational direction 1164 can be a clockwise direction or a counterclockwise direction.
- FIG. 11G (top view) and FIG. 11H (cross-sectional view) the rotational movement brings the latch features 1162 out of alignment with the protrusions 1156 , thus releasing the load on the second biasing member 634 .
- the second biasing member 634 can extend toward its unloaded length, thus driving the cap 1152 along the retraction direction 114 .
- the cap 1152 can be mechanically coupled to the skin-piercing feature 116 such that movement of the second biasing member 634 toward its unloaded length moves the skin-piercing feature 116 along the retraction direction 114 away from the patient's skin.
- the features of the deployment assembly 1100 and the retraction assembly 1150 can be varied as desired.
- various numbers, sizes, and/or shapes of the stop feature 1110 and/or aperture 1104 can be used.
- the stop feature 1110 includes one, two, three, four, five, or more tabs; and the aperture 1104 includes one, two, three, four, five, or more corresponding recesses.
- the number, size, and/or shape of the protrusions 1156 and/or latch features 1162 can be varied as desired.
- the retraction assembly 1150 can include one, two, three, four, five, or more protrusions; and one, two, three, four, five, or more latch features.
- the bodily fluid collection devices of the present technology can include a locking mechanism configured to prevent re-deployment of a skin-piercing feature after the skin-piercing feature has been deployed and retracted into the device.
- the locking mechanism is expected to improve safety by making the device single-use only, thus reducing the risk of injury or accidental reuse of a contaminated device.
- the locking mechanism includes a switchable feature that is movable between a pre-retraction configuration and a post-retraction configuration. The switchable feature can initially be in the pre-retraction configuration, and can be moved into the post-retraction configuration with the retraction of the skin-piercing feature.
- the switchable feature can constrain the movement of one or more device components (e.g., the actuator, plunger, skin-piercing assembly) to prevent the skin-piercing feature from being re-deployed even if the actuator is moved along the deployment direction.
- the switchable feature can constrain the one or more device components to move along a movement path that is different from a pre-retraction movement path and does not permit the skin-piercing feature to re-deploy.
- FIGS. 12A-12C are schematic cross-sectional illustrations of the operation of a locking mechanism 1200 configured in accordance with an embodiment the present technology.
- the locking mechanism 1200 can be incorporated into any embodiment of the bodily fluid collection devices disclosed herein.
- the locking mechanism 1200 can be incorporated into the device 100 of FIGS. 6A-10 .
- the locking mechanism 1200 can be used in combination with the actuation mechanism of FIGS. 11A-11H .
- the locking mechanism 1200 includes one or more switchable features 1202 and one or more guide features 1204 .
- the switchable features 1202 are on a component that is mechanically coupled to the skin-piercing feature 116 , such as a ring 122 ′ or the actuator 104 (not shown).
- the guide features 1204 can be on a component of the device that remains stationary relative to the skin-piercing feature 116 , such as the housing 102 (not shown).
- the switchable features 1202 are movable between a pre-retraction configuration and a post-retraction configuration. As shown in FIG. 12A , prior to movement of the actuator along the deployment direction 112 , the switchable features 1202 are initially in the pre-retraction configuration with their contact portions 1206 along a first surface 1208 A of the guide features 1204 . For example, in the pre-retraction configuration, the switchable features 1202 can be bent radially outward with the contact portions 1206 along an outer surface of the guide features 1204 . The first surface 1208 A applies a load to the contact portions 1206 to maintain the switchable features 1202 in the pre-retraction configuration and prevent the switchable feature 1202 from reverting to the post-retraction configuration.
- the contact portions 1206 of the switchable features 1202 slide along the deployment direction 112 against the first surface 1208 A until they reach the end portions 1210 of the guide features 1204 , releasing the load on the contact portions 1206 and allowing the switchable features 1202 to revert to the post-retraction configuration.
- the movement of the switchable features 1202 to the post-retraction configuration can include linear, radial, and/or rotational movements. In some embodiments, the movement of the switchable features 1202 only includes linear and/or radial movements and does not involve any rotational movements. For example, in the post-retraction configuration, the switchable features 1202 can be bent radially inward.
- the contact portions 1206 of the switchable features 1202 slide along the retraction direction 114 against a second surface 1208 B of the guide features 1204 .
- the second surface 1208 B can be an inner surface of the guide features 1204 .
- the switchable features 1202 can be biased toward the post-retraction configuration, such that the switchable features 1202 do not revert to the pre-retraction configuration even if the ring 122 ′ subsequently moves along the deployment direction 112 .
- the post-retraction configuration of the switchable features 1202 can constrain the movement of the ring 122 ′ to a movement path that prevents the skin-piercing feature 116 from being re-deployed.
- the ring 122 ′ can be disengaged from one or more device components (e.g., actuator, platform, collar, skin-piercing assembly) involved in deployment of the skin-piercing feature 116 while the ring 122 ′ moves along the movement path.
- FIGS. 12A-12C illustrate a mechanism 1200 with two switchable features and two guide features
- alternative embodiments may include any suitable number of switchable features and guide features.
- the mechanism 1200 can include one, two, three, four, five, or more switchable features; and one, two, three, four, five, or more guide features.
- the positioning of the switchable features and guide features can also be varied.
- the switchable features 1202 can be on the actuator, platform, collar, plunger, and/or skin-piercing assembly.
- FIGS. 12A-12C illustrate the contact portions 1206 of the switchable features 1202 being bent outward in the pre-retraction configuration and bent inward in the post-retraction configuration, in alternative implementations, the contact portions 1206 can be bent inward in the pre-retraction configuration and bent outward in the post-retraction configuration.
- the bodily fluid collection devices of the present technology can include a vacuum mechanism configured to apply a vacuum to the patient's skin to facilitate withdrawal of larger volumes of bodily fluid.
- the vacuum deforms the skin into a curved shape that opens the capillaries within the skin to increase the local flow of bodily fluid, and also maintains the incision in an opened configuration to promote withdrawal of bodily fluid into the device.
- the vacuum can be applied by expanding the volume within a flexible membrane, such as the sealing member 124 described above, as opposed to actively drawing air out of a rigid cup (e.g., withdrawing air from a suction cup.)
- the timing of vacuum application relative to the other steps in the operation of the bodily fluid collection device can be varied as desired.
- the vacuum can be applied prior to, concurrently with, and/or after the deployment of the skin-piercing feature to pierce the skin.
- the vacuum can be applied prior to, concurrently with, and/or after the retraction of the skin-piercing feature away from the skin.
- the vacuum mechanisms of the present technology can be used in combination with any of the actuation mechanisms disclosed herein, such as the actuation mechanisms described with reference to FIGS. 4-12C .
- FIGS. 13A-13D are schematic cross-sectional illustrations of a vacuum being applied to a patient's skin 250 configured in accordance with an embodiment the present technology.
- the device is initially applied to the patient's body with the housing 102 and opening 108 against the skin 250 ( FIG. 13A ).
- a vacuum is applied to the skin 250 to pull at least a portion of the skin 250 into a curved shape ( FIG. 13B ).
- the skin 250 can be pulled at least partially into the device, such as being pulled at least partially through the opening 108 and into the interior of the housing.
- a skin-piercing feature 116 is deployed and pierces the skin 250 to create an incision 1300 ( FIG. 13C ).
- the skin-piercing feature 116 can be then retracted to permit bodily fluid to flow from the incision 1300 into the housing 102 ( FIG. 13D ).
- FIGS. 14A-14C are schematic cross-sectional illustrations of a vacuum being applied to a patient's skin 250 configured in accordance with an embodiment the present technology.
- the device is initially applied to the patient's body with the housing 102 and opening 108 against the skin 250 ( FIG. 14A ).
- a vacuum is applied to the skin 250 to pull at least a portion of the skin 250 into a curved shape ( FIG. 14B ).
- the skin 250 can be pulled at least partially into the device, such as through the opening 108 and into the interior of the housing 102 , and the skin-piercing feature 116 can pierce the skin 250 to create an incision 1300 .
- the skin-piercing feature 116 is held stationary as the skin 250 is pulled into contact with the skin-piercing feature 116 .
- the skin-piercing feature 116 can be concurrently deployed toward the skin 250 as the vacuum is applied. The skin-piercing feature 116 can then be retracted to permit bodily fluid to flow from the incision 1300 into the housing 102 ( FIG. 14C ).
- the bodily fluid collection device does not include a pre-existing vacuum source.
- the device includes a vacuum mechanism that generates a vacuum along with the deployment and/or retraction of the skin-piercing feature (“dynamically-generated vacuum”).
- the vacuum mechanism can include a lumen that is initially at or near atmospheric pressure (e.g., gauge pressure is about 0 kPa).
- gauge pressure is about 0 kPa.
- the vacuum mechanism can lower the pressure within the lumen to less than atmospheric pressure by expanding the volume of the lumen as opposed to withdrawing gas from the lumen, thereby creating a vacuum within the lumen.
- the lumen can be at a gauge pressure less than or equal to about ⁇ 10 kPa, ⁇ 15 kPa, ⁇ 20 kPa, ⁇ 25 kPa, ⁇ 30 kPa, ⁇ 35 kPa, ⁇ 40 kPa, ⁇ 45 kPa, ⁇ 50 kPa, ⁇ 55 kPa, or ⁇ 60 kPa.
- the lumen can be in fluidic connection with the skin, or a device component that contacts the skin (e.g., the flexible membrane), to apply the vacuum directly or indirectly to the skin.
- the lumen is mechanically coupled to one or more movable components of the bodily fluid collection device, such that movement of the component along the deployment direction decreases the volume of the lumen, and movement of the component along the retraction increases the volume of the lumen.
- the lumen can be at least partially formed from a sealing member (e.g., a flexible membrane) that is deformable to increase or decrease the volume of the lumen.
- the lumen can be formed from 2 solid cylinders in contact that are able to slide one relative to the other.
- the vacuum mechanism can further include at least one valve fluidically connected to the lumen to control air flow into and out of the lumen.
- the valve can be a one-way valve (e.g., a check valve) that permits air to escape from within the lumen as the lumen volume decreases, but prevents air from entering the lumen as the lumen volume increases to dynamically generate a vacuum within the lumen.
- the valve can be mechanically shut as the actuation mechanism reaches a predetermined position prior or at the same time as full actuation.
- FIGS. 15A-15C are schematic cross-sectional illustrations of the operation of a dynamically-generated vacuum mechanism 1500 configured in accordance with an embodiment the present technology.
- the vacuum mechanism 1500 includes the sealing member 124 , which is at least partially over the opening 108 in the housing 102 of the bodily fluid collection device.
- the sealing member 124 has an outer portion 1502 A and an inner portion 1502 B.
- the outer portion 1502 A of the sealing member 124 is connected to the housing 102
- the inner portion 1502 B of the sealing member 124 is connected to the plunger 122 , thus a forming a lumen 126 in fluidic connection with the opening 108 .
- the plunger 122 includes the valve 128 (e.g., an umbrella valve) in fluidic connection with the lumen 126 .
- the plunger 122 can be connected to the skin-piercing assembly 106 (not shown), as described herein.
- the device is initially applied to the patient's body with the opening 108 against the patient's skin, such that the lumen 126 is sealed between the sealing member 124 , plunger 122 , housing 102 , and the skin.
- the pressure within the lumen 126 Prior to movement of the actuator of the device ( FIG. 15A ), the pressure within the lumen 126 is at or near atmospheric pressure, and the valve 128 is closed.
- the actuator is moved along the deployment direction (e.g., to deploy the skin-piercing feature)
- the plunger 122 also moves along the deployment direction toward the opening 108 , thus reducing the volume of the lumen 126 ( FIG. 15B ).
- valve 128 can be configured to open when the gauge pressure within the lumen is greater than or equal to about 0.1 kPa, 0.2 kPa, 0.3 kPa, 0.4 kPa, 0.5 kPa, 0.6 kPa, 0.7 kPa, 0.8 kPa, 0.9 kPa, 1.0 kPa, 1.5 kPa, 2 kPa, 2.5 kPa, 3.0 kPa, or 4 kPa.
- the volume of the lumen 126 increases ( FIG. 15C ).
- the valve 128 prevents air from entering the lumen 126 as the volume increases, thus producing a corresponding decrease in pressure within the lumen 126 .
- the decreased pressure produces a vacuum that pulls the patient's skin at least partially into the device (e.g., pulls the skin at least partially through the opening 108 and into the lumen 126 ).
- the bodily fluid collection device 100 can include a dynamically-generated vacuum mechanism configured in accordance with an embodiment the present technology.
- the vacuum mechanism includes the sealing member 124 .
- the sealing member 124 is coupled to the housing 102 and plunger 122 to define the lumen 126 .
- the sealing member 124 can be movable between a collapsed configuration in which the volume of the lumen 126 is decreased, and an extended configuration in which the volume of the lumen 126 is increased.
- the sealing member 124 is mechanically coupled to the plunger 122 so that the movement of the plunger 122 also moves the sealing member 124 between the collapsed and extended configurations.
- the sealing member 124 , housing 102 , and plunger 122 can be connected to each other via airtight connections to allow for creation of a low-pressure region (e.g., a vacuum) within the lumen 126 .
- a low-pressure region e.g., a vacuum
- the outer portion 1502 A of the sealing member 124 is coupled between the housing 102 and a retaining element 640 .
- the retaining element 640 can be a ring-like structure that compresses the outer portion 1502 A against a cylindrical portion 642 of the housing 102 to create an airtight connection between the sealing member 124 and the housing 102 .
- the inner portion 1502 B of the sealing member 124 is connected to the upper surface of the plunger 122 .
- the valve 128 (e.g., an umbrella valve) extends through the upper surface of the plunger 122 to control air flow into and out of the lumen 126 .
- the pressure within the lumen 126 Prior to movement of the actuator of the device ( FIG. 6A ), the pressure within the lumen 126 is at or near atmospheric pressure, and the valve 128 is closed.
- the plunger 122 moves along the deployment direction 112 , thus moving the sealing member 124 into the collapsed configuration and reducing the volume of the lumen 126 .
- the reduction in volume produces a corresponding increase in the pressure within the lumen 126 , causing the valve 128 to open and permit air to escape from within the lumen 126 .
- the plunger 122 moves along the retraction direction 114 , thus pulling the sealing member 124 into the extended configuration and increasing the volume of the lumen 126 .
- the valve 128 prevents air from entering the lumen 126 as the volume increases, thus producing a corresponding decrease in pressure within the lumen 126 .
- the decreased pressure produces a vacuum that pulls the patient's skin at least partially through the opening 108 and into the lumen 126 .
- FIGS. 16A-16C are schematic cross-sectional illustrations of the operation of another dynamically-generated vacuum mechanism 1600 configured in accordance with an embodiment the present technology.
- the vacuum mechanism 1600 includes the sealing member 124 connected to the housing 102 and the plunger 122 to form the lumen 126 .
- the lumen 126 is in fluidic connection with one or more openings 108 in the housing 102 .
- the plunger 122 includes the valve 128 in fluidic connection with the lumen 126 .
- the housing 102 includes a prong 1602 extending into the lumen 126 toward the valve 128 .
- the valve 128 can be a mechanically actuated valve that is opened and/or closed by engagement with the prong 1602 .
- the device is initially applied to the patient's body with the opening 108 against the patient's skin, such that the lumen 126 is sealed between the sealing member 124 , plunger 122 , housing 102 , and the skin.
- the pressure within the lumen 126 Prior to movement of the actuator of the device ( FIG. 16A ), the pressure within the lumen 126 is at or near atmospheric pressure, and the valve 128 is closed.
- the actuator When the actuator is moved along the deployment direction (e.g., to deploy the skin-piercing feature), the plunger 122 also moves along the deployment direction toward the opening 108 , thus bringing the prong 1602 in contact with the valve 128 ( FIG. 16B ).
- the prong 1602 can engage and open the valve 128 to permit air to escape from within the lumen 126 .
- the prong 1602 When the plunger 122 moves along the retraction direction away from the opening (e.g., when the skin-piercing feature is retracted), the prong 1602 is disengaged from the valve 128 ( FIG. 16C ). The prong 1602 can close the valve 128 as it disengages from the valve 128 , thus preventing air from entering the lumen 126 . Accordingly, as the volume of the lumen 126 increases, the pressure within the lumen 126 decreases, producing a vacuum that pulls the patient's skin at least partially through the openings 108 and into the lumen 126 .
- FIGS. 17A and 17B are schematic cross-sectional illustrations of the operation of a dynamically-generated vacuum mechanism 1700 integrated into the skin-piercing assembly 106 configured in accordance with an embodiment the present technology.
- the skin-piercing assembly 106 itself forms part of the valve 128 .
- the valve 128 can include a valve member 1702 (e.g., a disk, seal, or gasket) and an opening 1704 that connects to the vacuum lumen (not shown).
- the valve member 1702 can be made of rubber or a similar material that forms an airtight seal when placed against the opening 1704 .
- the valve member 1702 can be on the skin-piercing assembly 106 , such as near the skin-piercing feature 116 .
- the skin-piercing assembly 106 can be at least partially within the plunger 122 , and the opening 1704 can be formed in the plunger 122 .
- the valve 128 can be opened when the valve member 1702 is away from the opening 1704 (e.g., prior to deployment of the skin-piercing feature 116 ) ( FIG. 17A ).
- the valve 128 can be closed when the skin-piercing feature and the valve member 1702 is against the opening 1704 (e.g., after deployment of the skin-piercing feature 116 ) ( FIG. 17B ).
- FIGS. 18A and 18B are cross-sectional views of a bodily fluid collection device 100 having a dynamically-generated vacuum mechanism integrated into the skin-piercing assembly 106 configured in accordance with an embodiment the present technology.
- the device 100 includes the housing 102 , the actuator 104 , and the skin-piercing assembly 106 .
- the housing 102 includes the upper housing portion 602 A and the lower housing portion 602 B.
- the upper housing portion 602 A is shaped to receive the actuator 104 .
- the lower housing portion 602 B includes the bottom surface 110 having the opening 108 .
- the actuator 104 is at least partially within the upper housing portion 602 A of the device 100 .
- the actuator 104 is mechanically coupled to the skin-piercing assembly 106 via one or more internal device components, such as the platform 120 , plunger 122 , and/or sealing member 124 .
- the actuator 104 is positioned around at least a portion of the platform 120
- the platform 120 is positioned around at least a portion of the plunger 122 and/or sealing member 124 .
- the actuator 104 , platform 120 , plunger 122 , and/or sealing member 124 can be concentrically positioned, such that the longitudinal axes of these components are aligned.
- the actuator 104 , platform 120 , plunger 122 , and sealing member 124 can be coupled to each other using any suitable combination of complementary interconnecting features (e.g., notches, grooves, projections, tabs, and the like).
- the platform 120 can include one or more hook features 1802 that engage one or more complementary notch features 1804 on the plunger 122 , such that movement of the platform 120 along the deployment direction 112 also moves the plunger 122 along the deployment direction.
- the plunger 122 can be a hollow structure with an upper portion 1806 A and a lower portion 1806 B. The upper portion 1806 A can be coupled to the platform 120 , and the lower portion 1806 B can be coupled to the sealing member 124 .
- the skin-piercing assembly 106 includes a shaft 1808 at least partially within the plunger 122 .
- the shaft 1808 has an upper end portion 1810 A, a lower end portion 1810 B, and a flared portion 1810 C.
- the longitudinal axis of the shaft 1808 can be aligned with the deployment direction 112 such that the upper end portion 1810 A is away from the opening 108 and the lower end portion 1810 B is toward the opening 108 .
- the flared portion 1810 C can be between the upper end portion 1810 A and the lower end portion 1810 B.
- the flared portion 1810 C can have a larger diameter than the upper end portion 1810 A and the lower end portion 1810 B.
- the shaft 1808 is movable relative to the plunger 122 along the deployment direction 112 and the retraction direction 114 .
- the skin-piercing assembly 106 further includes the skin-piercing feature 116 and the biasing member 118 .
- the skin-piercing feature 116 is coupled to the lower end portion 1810 B of the shaft 1808 .
- the biasing member 118 is positioned within the plunger 122 around at least a portion of the shaft 1808 .
- the biasing member 118 is coupled between the flared portion 1806 C of the shaft 1808 and the platform 120 , such that the biasing member 118 drives the shaft 1808 downward relative to the plunger 122 during deployment of the skin-piercing feature 116 .
- the sealing member 124 includes the outer portion 1502 A and the inner portion 1502 B.
- the outer portion 1502 A is connected to the housing 102 and the inner portion 1502 B is connected to the plunger 122 , thus forming a lumen 126 in fluidic connection with the opening 108 .
- the lower portion 1806 B of the plunger 122 includes a collar 1812 that is received within a corresponding groove 1814 in the inner portion 1502 B of the sealing member 124 to form an airtight seal between the plunger 122 and sealing member 124 .
- the skin-piercing assembly 106 , plunger 122 , and sealing member 124 collectively form a valve 128 fluidically connected to the lumen 126 .
- the lower portion 1806 B of the plunger 122 and the inner portion 1502 B of the sealing member 124 can be open so as to form the opening 1704 of the valve 128 .
- the flared portion 1810 C of the shaft 1808 of the skin-piercing assembly 106 can serve as the valve member 1702 of the valve 128 .
- the valve 128 can be opened when the valve member 1702 is away from the opening 1704 (e.g., when the flared portion 1810 C of the shaft 1808 is toward the upper portion 1806 A of the plunger 122 ) ( FIG. 18A ).
- the valve 128 can be closed when the valve member 1702 is against the opening 1704 (e.g., when the flared portion 1810 C of the shaft 1808 is toward the lower portion 1806 B of the plunger 122 ) ( FIG. 18B ).
- the device is initially applied to the patient's body with the opening 108 against the patient's skin, such that the lumen 126 is sealed between the sealing member 124 , plunger 122 , housing 102 , and the skin.
- the pressure within the lumen 126 Prior to deployment of the skin-piercing feature 116 ( FIG. 18A ), the pressure within the lumen 126 is at or near atmospheric pressure.
- the valve 128 Prior to deployment of the skin-piercing feature 116 ( FIG. 18A ), the pressure within the lumen 126 is at or near atmospheric pressure.
- the valve 128 is in the open state, with the valve member 1702 is away from the opening 1704 .
- the biasing member 118 drives the shaft 1808 along the deployment direction 112 so that the skin-piercing feature 116 is moved toward the opening 108 .
- the movement of the shaft 1808 also drives the valve member 1702 against the opening 1704 , thus closing the valve 128 .
- the second biasing member 634 is between the platform 120 and the housing 102 , and drives the platform 120 along the retraction direction 114 .
- the movement of the platform 120 produces a corresponding movement of the plunger 122 along the retraction direction 114 .
- the movement of the plunger 122 pulls the inner portion 1502 B of the sealing member 124 along the retraction direction 114 , resulting in an increase in volume of the lumen 126 .
- the shaft 1808 maintains its deployed position relative to the plunger 122 such that the valve 128 remains closed, preventing air from entering the lumen 126 ( FIG. 18B ). Accordingly, the pressure within the lumen 126 decreases, producing a vacuum that pulls the patient's skin at least partially through the opening 108 and into the lumen 126 .
- the bodily fluid collection devices of the present technology include a skin interface that interacts with the patient's skin and/or bodily fluid to enhance withdrawal of the bodily fluid into the device.
- the skin interface can control a curvature of the skin pulled into the device (e.g., via the vacuum mechanisms described herein with reference to FIGS. 13A-18B ) to maintain the incision in an open position that facilitates flow of bodily fluid from the skin.
- Other purposes of the skin interface is to present a controlled surface on which to collect and direct the flowing bodily fluids to prevent fouling or contamination from the surface of the skin and maintain the skin of the user cleaner.
- the skin interface is configured to facilitate rapid removal of bodily fluid from the skin to reduce coagulation of the bodily fluid and/or reduce activation of components within the bodily fluid.
- the skin interface can be configured to quickly remove blood from the skin to reduce blood coagulation and/or platelet activation.
- FIGS. 19A-19E are schematic cross-sectional illustrations of skin interfaces to control skin curvature configured in accordance with an embodiment the present technology.
- FIG. 19A illustrates a skin interface 1900 including the housing 102 with the opening 108 .
- a vacuum is applied to the skin 250 from within the housing 102 , a portion of the skin 250 is pulled through the opening 108 and assumes a curved shape.
- FIG. 19B illustrates a skin interface 1900 including a curved housing portion 1902 .
- the curved housing portion 1902 can be located at least partially around the opening 108 in the housing 102 .
- a vacuum is applied to the skin 250 from within the housing 102 , the skin 250 is pulled toward the opening 108 and against the bottom surface of the curved housing portion 1902 , thus assuming a curvature similar to the curvature of the curved housing portion 1902 .
- FIG. 19C illustrates a skin interface 1900 including a relatively thin flexible membrane 130 .
- the membrane 130 has a thickness less than or equal to about 250 ⁇ m, or within a range from about 50 ⁇ m to about 400 ⁇ m.
- the flexible membrane 130 is coupled to the housing 102 in a position at least partially covering the opening 108 .
- the membrane 130 optionally includes an aperture 1904 to allow the skin-piercing feature (not shown) to pass through.
- An adhesive may be applied to the bottom surface of the membrane 130 to facilitate sealing against the skin 250 .
- the membrane 130 When the membrane 130 is exposed to a vacuum from within the housing 102 , the membrane 130 is pulled at least partially into the interior of the housing 102 and assumes a curved shape. Due to the seal between the skin 250 and the membrane 130 , the skin 250 is also pulled toward the opening 108 and assumes a curvature similar to the curvature of the membrane 130 .
- FIG. 19D illustrates a skin interface 1900 including a relatively thick flexible membrane 130 .
- the skin interface 1900 is similar to the interface of FIG. 19C except that the flexible membrane 130 has an increased thickness.
- the membrane 130 has a thickness greater than or equal to about 400 mm, or within a range from about 400 mm to about 800 mm.
- a thinner membrane exhibits a higher curvature when exposed to vacuum and produces a higher skin curvature
- a thicker membrane exhibits a lower curvature when exposed to vacuum and produces a lower skin curvature.
- a higher skin curvature can be advantageous for maintaining the incision in an opened configuration, while a lower skin curvature can be advantageous for reducing bruising or other injuries to the surrounding portions of the skin 250 .
- FIG. 19E illustrates a skin interface 1900 including a flexible membrane 130 with variable thickness.
- the skin interface 1900 is similar to the interfaces of FIG. 19C-19D , except that the flexible membrane 130 has a variable thickness.
- the membrane 130 has a central portion 1906 A and an outer portion 1906 B.
- the central portion 1906 A can be thinner and have a higher curvature when exposed to vacuum, while the outer portion 1906 B can be thicker and have a lower curvature when exposed to vacuum.
- the central portion 1906 A can have a thickness less than or equal to about 300 ⁇ m, or within a range from about 50 mm to about 300 ⁇ m; and the outer portion 1906 B can have a thickness greater than or equal to about 300 ⁇ m, or within a range from about 300 ⁇ m to about 600 ⁇ m.
- the portion of the skin 250 near the central portion 1906 A can have a higher curvature than the portion of the skin 250 near the outer portion 1906 B. This configuration can be advantageous for maintaining the incision in an open position while reducing injuries to other portions of the skin 250 .
- the thicknesses of the central portion 1906 A and outer portion 1906 B can be reversed, such that the central portion 1906 A is thicker than the outer portion 1906 B.
- the flexible membrane provides more precise control of the curvature of the skin than is achievable using vacuum pressure alone, even over relatively large skin surface areas. Accordingly, a bodily fluid collection device utilizing a flexible membrane as a skin interface can have a larger opening in the housing to allow for bodily fluid to be withdrawn from a greater skin surface area, thus increasing the potential draw volume.
- the diameter of the opening can be at least about 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm, 16 mm, 17 mm, 18 mm, 19 mm, 20 mm, 21 mm, 22 mm, 23 mm, 24 mm, 25 mm, 26 mm, 27 mm, 28 mm, 29 mm, or 30 mm. In some embodiments, the diameter is within a range from about 9 mm to about 27 mm.
- FIG. 20 is a block diagram of a method 2000 for withdrawing bodily fluid from a patient's skin using a flexible membrane configured in accordance with an embodiment the present technology.
- the method 2000 can be applied to any embodiment of the bodily fluid collection devices disclosed herein, such as the device 100 . Additionally, one or more steps of the method 2000 can be combined with or substituted for any of the steps of the other methods disclosed herein. For example, one or more steps of the method 2000 can be performed in combination with or as sub-steps of block 340 and/or block 350 of the method 300 .
- the method 2000 includes drawing a vacuum within the device (block 2010 ).
- the vacuum can be generating using any of the vacuum mechanisms disclosed herein, such as the vacuum mechanisms described with reference to FIGS. 13A-18B .
- the method 2000 further includes pulling a flexible membrane at least partially within the device (block 2020 ).
- the flexible membrane can be coupled to the bottom surface of the housing in a position covering at least a portion of the opening, and the flexible membrane can be pulled at least partially through the opening when exposed to the vacuum.
- the method further includes contacting a patient's skin with the flexible membrane to control a curvature of the skin (block 2030 ).
- the patient's skin is also pulled at least partially through the opening and into the device.
- the flexible membrane can assume a curved shape when exposed to the vacuum, and the patient's skin can be sealed against the flexible membrane so as to assume a similar curved shape.
- FIGS. 21A-21C are cross-sectional and perspective views of the flexible membrane 130 of a bodily fluid collection device configured in accordance with an embodiment the present technology.
- the device includes the opening 108 formed in the housing 102 , and the membrane 130 is coupled to the housing 102 and covers at least a portion of the opening 108 .
- the membrane 130 can include an aperture 1904 to allow the skin-piercing feature of the device to pass through the membrane 130 during deployment.
- the membrane 130 may be provided without any aperture, and the skin-piercing feature can puncture the membrane 130 during deployment to form the aperture 1904 .
- the membrane 130 Prior to being exposed to a vacuum ( FIG. 21A ), the membrane 130 is in a generally planar configuration, with little or no curvature.
- the membrane 130 When a vacuum is drawn within the housing 102 of the device ( FIG. 21B ), the membrane 130 is pulled at least partially within the housing 102 and into a curved shape. Bodily fluid is withdrawn into the housing 102 via the aperture 1904 , and can be directed into a collection reservoir (not shown) via a channel 2100 .
- FIG. 22 is an exploded view of the flexible membrane 130 configured in accordance with an embodiment the present technology.
- the membrane 130 includes a film 2200 , a first adhesive layer 2202 , and a second adhesive layer 2204 .
- the film 2200 can be a thin film of a flexible material, such as polyurethane or silicone.
- the first adhesive layer 2202 can be a double-sided adhesive that adheres to both the film 2200 and the housing of the bodily fluid collection device.
- the second adhesive layer 2204 can be a double-sided adhesive that adheres to both the film 2200 and a portion of the patient's skin.
- the adhesive material of the first and second adhesive layers 2202 , 2204 can be selected such that when the device is applied to the patient's body, the flexible membrane 130 forms an airtight seal between the housing and the patient's skin.
- the first adhesive layer 2202 , second adhesive layer 2204 , or both may be omitted from the membrane 130 .
- the film 2200 can include an aperture 1904 for the skin-piercing feature to pass through during deployment.
- the first adhesive layer 2202 can include an aperture 2206 formed within a central portion of the first adhesive layer 2202 .
- the second adhesive layer 2204 can include an aperture 2208 formed within a central portion of the second adhesive layer 2204 .
- the apertures 2206 , 2208 can have a size and/or shape similar to the size and/or shape of the opening in the housing.
- the membrane 130 can be provided with a liner 2210 that protects the membrane 130 prior to use, e.g., during storage and/or transportation.
- the liner 2406 can be removed to expose the second adhesive layer 2204 so that the flexible membrane 130 can be applied to and sealed against the patient's skin.
- the liner 2210 can include a tab portion 2212 that extends beyond the housing of the device (e.g., as shown in FIG. 6A ) to facilitate removal of the liner 2210 .
- the membrane can be directly cast into the base of the bodily fluid collection device itself using thermoplastic elastomeric materials or silicone materials. This manufacturing method would remove the need for the first adhesive layer 2202 and as these manufacturing methods do not require the membrane to be planar, they would enable the creation of structural or functional features on the membrane itself.
- the flexible membranes of the present technology include one or more surface features and/or treatments to enhance flow of the bodily fluid from the patient's skin and into the device.
- the surface features and/or treatments can be configured to reduce coagulation of the bodily fluid (e.g., blood coagulation), reduce adhesion of the bodily fluid to the patient's skin, reduce adhesion of the bodily fluid to the membrane, direct flow of the bodily fluid toward a desired location (e.g., toward the collection reservoir), and/or direct flow of the bodily fluid away from an undesired location.
- the surface features and/or treatments can be on a lower surface of the membrane (e.g., the surface toward the patient's skin), the upper surface of the membrane (e.g., the surface away from the patient's skin), or both.
- the upper and lower surfaces of the membrane can have the same features and/or treatments, or can have different features and/or treatments.
- FIGS. 23A-23E are various views of portions of flexible membranes with different surface features and/or treatments configured in accordance with an embodiment the present technology.
- FIG. 23A is a schematic illustration of a top view of the flexible membrane 130 without surface features and/or treatments.
- the membrane 130 includes an aperture 1904 (e.g., pre-formed in the membrane 130 or formed by the skin-piercing feature) through which bodily fluid 2300 is withdrawn from the patient's skin 250 .
- the fluid 2300 may spread and smear across the skin 250 and/or membrane 130 , thus making it more difficult to collect the fluid 2300 .
- FIG. 23B is a schematic illustration of a top view of the flexible membrane 130 with micropatterned features 2302 .
- the micropatterned features 2302 can include various combinations of channels, ridges, grooves, surface modifications, or patterned surface treatments or coatings, and the like.
- the micropatterned features 2302 can be shaped and positioned to direct flow of the bodily fluid toward a desired location, such as toward the collection reservoir.
- the micropatterned features 2302 include a linear channel 2304 extending from the aperture 1904 toward the reservoir. Bodily fluid 2300 withdrawn from the skin 250 can flow into the channel 2304 and toward the reservoir.
- these features can be used to combine the bodily fluids from multiple incisions or alternatively to keep them separate and allow different treatments to be made to the flowing fluids. Furthermore, this approach can allow the direction of the multiple flows of bodily fluids toward different or separate reservoirs or containers.
- FIG. 23C is a perspective top view of a portion of the flexible membrane 130 with micropatterned features 2302 .
- the features 2302 include a circular ridge 2306 defining a chamber 2308 that contains the bodily fluid.
- the ridge 2306 can define an opening 2310 in the chamber 2308 that is oriented toward the collection reservoir to direct the bodily fluid into the reservoir.
- the features 2302 can also include ridges, parallel ridges 2312 , or multiple ridges within the chamber 2308 .
- the ridges 2312 can be on either side of the location where the skin-piercing feature punctures the membrane 130 to direct bodily fluid toward the opening 2310 , or along the path of the flow to act as a capillary guidance to the flow of fluids.
- the features 2302 can also include a pair of angled ridges 2314 within the chamber 2308 near the opening 2310 .
- the angled ridges 2314 can serve to funnel bodily fluid from within the chamber 2308 toward the opening 2310 .
- FIG. 23D is a schematic illustration of a top view of a portion of the flexible membrane 130 with a hydrophobic coating 2316 (e.g., a silicone coating).
- the hydrophobic coating 2316 can be applied to the membrane 130 (e.g., by spray-coating).
- the membrane 130 itself can be made of a hydrophobic material.
- FIG. 23E is a schematic illustration of a top view of a portion of the flexible membrane 130 with an anticoagulant coating 2318 .
- the anticoagulant coating 2318 includes spray-coated EDTA.
- the anticoagulant coating 2318 can reduce the coagulation of the bodily fluid, thus improving flow into the reservoir.
- FIGS. 24A-24F are cross-sectional views of housing features to control flow of bodily fluid along a flexible membrane 130 configured in accordance with an embodiment the present technology.
- accumulation of bodily fluid 2300 at the outer portion 1906 B of the flexible membrane 130 is undesirable.
- Such accumulation may occur if the angle between the outer portion 1906 B and the portion of the housing 102 adjacent to the outer portion 1906 B (“base portion 2400 ”) is sufficiently small, e.g., less than about 90 degrees.
- the angle between the outer portion 1906 B and the base portion 2400 may initially be greater than or equal to about 90 degrees ( FIG. 24A ), the angle may decrease to less than 90 degrees when the membrane 130 is curved ( FIG. 24B ).
- the decreased angle may pull bodily fluid between the outer portion 1906 B and the base portion 2400 , e.g., via capillary action.
- FIGS. 24C and 24D illustrate a shelf 2402 to reduce flow of bodily fluid between the outer portion 1906 B and the base portion 2400 .
- the shelf 2402 can be formed in the base portion 2400 and can extend radially inward to partially cover the opening 108 .
- bodily fluid 2300 can flow onto the shelf 2402 , rather than becoming trapped between the base portion 2400 and the membrane 130 .
- FIGS. 24E and 24F illustrate an angled base portion 2400 to reduce flow of bodily fluid between the outer portion 1906 B and the base portion 2400 .
- the geometry of the angled based portion 2400 can be configured such that when the membrane 130 is curved ( FIG. 24F ), the angle between the base portion 2400 and the outer portion 1906 B of the membrane 130 is sufficiently large to avoid drawing bodily fluid 2300 between the outer portion 1906 B and the base portion 2400 .
- FIGS. 25A-25F are cross-sectional and top views of a wicking element 2500 for directing flow of a bodily fluid 2300 configured in accordance with an embodiment the present technology.
- the wicking element 2500 can be used in combination with or as an alternative to the flexible membranes disclosed herein.
- the wicking element 2500 can be made of an absorbent material, and can optionally include an anticoagulant.
- the wicking element 2500 can include a first wicking portion 2502 A and a second wicking portion 2502 B.
- the first wicking portion 2502 A can be shaped to at least partially cover the opening 108 of the housing 102 , and can optionally include an aperture for the skin-piercing feature 116 to pass through.
- the second wicking portion 2502 B can have an elongated shape configured to direct bodily fluid 2300 into the housing 102 toward the collection reservoir.
- the wicking element 2500 is positioned over the flexible membrane 130 , with the first wicking portion 2502 A over the aperture 1904 in the membrane 130 , and the second wicking portion 2502 B extending along the membrane 130 toward the interior of the housing ( FIG. 25A (cross-sectional view) and 25 B (top view)).
- the skin-piercing feature 116 can be deployed through the first wicking portion 2502 A to pierce the patient's skin ( FIG. 25C (cross-sectional view) and 25 D (top view)).
- the skin-piercing feature 116 can subsequently be retracted through the first wicking portion 2502 A to permit withdrawal of bodily fluid 2300 ( FIG. 25E (cross-sectional view) and 25 F (top view)).
- a first portion of the bodily fluid 2300 can be absorbed into the wicking element 2500 .
- the wicking element 2500 can be used to absorb and discard the first portion of the bodily fluid 2300 , while directing the remaining portion of the bodily fluid 2300 into the housing and reservoir for collection.
- the wicking element can be utilized to guide the flow of fluids over the membrane or plastic and deliver chemical treatments to the fluid rapidly after it is extracted from the skin.
Abstract
Description
- The present application claims the benefit of U.S. Provisional Patent Application No. 62/731,728, filed Sep. 14, 2018, and titled “BODILY FLUID COLLECTION DEVICES AND RELATED METHODS,” the disclosure of which is incorporated herein by reference in its entirety.
- This application is related to U.S. application Ser. No. 13/750,526, filed Jan. 25, 2013, entitled “Handheld Device for Drawing, Collecting, and Analyzing Bodily Fluid”; U.S. application Ser. No. 13/949,108, filed Jul. 23, 2013, entitled “Methods, Systems, and Devices Relating to Open Microfluidic Channels”; U.S. application Ser. No. 14/816,994, filed Aug. 3, 2015, entitled “Devices, Systems and Methods for Gravity-Enhanced Microfluidic Collection, Handling and Transferring of Fluids”; U.S. application Ser. No. 15/387,177, filed Dec. 21, 2016, entitled “Devices, Systems and Methods for Actuation and Retraction in Fluid Collection”; U.S. application Ser. No. 15/711,746, filed Sep. 21, 2017, entitled “Methods for Delivery of Bodily Fluids Onto a Fibrous Substrate”; and U.S. Provisional Application No. 62/533,323, filed Jul. 17, 2017, entitled “Apparatus, Systems and Methods for Preparing and Shipping”; all of which are incorporated herein by reference in their entireties.
- The present technology is related to collecting bodily fluid from a patient. In particular, various embodiments of the present technology are related to handheld bodily fluid collection devices and related methods.
- Devices, systems and methods to collect bodily fluids, such as blood, are widely used in personalized, clinical and field medical applications. Biological samples are commonly collected using simple lancing devices or more sophisticated devices that require trained personnel (e.g., phlebotomy venipunctures). Transferring bodily fluids to a container, receptacle or an analysis device often requires several steps, which can be time consuming, prone to error and/or cumbersome. Moreover, many personalized devices designed for untrained users can obtain only very limited volumes of bodily fluid, which in turn limits the applicability of such devices.
- Many aspects of the present technology can be better understood with reference to the following drawings. The components in the drawings are not necessarily to scale. Instead, emphasis is placed on illustrating clearly the principles of the present technology. For ease of reference, throughout this disclosure identical reference numbers may be used to identify identical or at least generally similar or analogous components or features.
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FIG. 1A is a perspective view of a bodily fluid collection device configured in accordance with an embodiment of the present technology. -
FIG. 1B is a perspective view of the bodily fluid collection device ofFIG. 1A in use. -
FIG. 1C is a perspective view illustrating detachment of the collection reservoir from the bodily fluid collection device ofFIG. 1A . -
FIG. 2A is a schematic cross-sectional illustration of a bodily fluid collection device configured in accordance with an embodiment of the present technology. -
FIG. 2B is a side view of a skin-piercing feature configured in accordance with the present technology. -
FIG. 2C is a side view of a skin-piercing feature with a stop feature configured in accordance with the present technology. -
FIG. 3 is a block diagram of a method for using a bodily fluid collection device in accordance with an embodiment of the present technology. -
FIG. 4 is a block diagram of a method for deploying a skin-piercing feature using an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology. -
FIGS. 5A-5C are schematic cross-sectional illustrations of the operation of an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology. -
FIG. 6A is a cross-sectional view of a bodily fluid collection device with an in situ loaded actuation mechanism configured in accordance with an embodiment of the present technology. -
FIG. 6B is a cross-sectional view of internal components of the device ofFIG. 6A . -
FIG. 6C is a top view of internal components of the device ofFIG. 6A . -
FIG. 6D is a perspective view of internal components of the device ofFIG. 6A . -
FIG. 6E is an exploded view of internal components of the device ofFIG. 6A . -
FIG. 7 is a cross-sectional view of the device ofFIG. 6A in a deployment state. -
FIG. 8 is a cross-sectional view of the device ofFIG. 6A in a peak deployment state. -
FIG. 9 is a cross-sectional view of the device ofFIG. 6A in a retraction state. -
FIG. 10 is a cross-sectional view of the device ofFIG. 6A in a re-actuation state. -
FIGS. 11A-11H are schematic top and cross-sectional illustrations of the operation of a pre-loaded actuation mechanism in accordance with the present technology. -
FIGS. 12A-12C are schematic cross-sectional illustrations of the operation of a locking mechanism configured in accordance with an embodiment of the present technology. -
FIGS. 13A-13D are schematic cross-sectional illustrations of a vacuum being applied to a patient's skin in accordance with an embodiment of the present technology. -
FIGS. 14A-14C are schematic cross-sectional illustrations of a vacuum being applied to a patient's a patient's skin in accordance with an embodiment of the present technology. -
FIGS. 15A-15C are schematic cross-sectional illustrations of the operation of a dynamically-generated vacuum mechanism in accordance with an embodiment of the present technology. -
FIGS. 16A-16C are schematic cross-sectional illustrations of the operation of another dynamically-generated vacuum mechanism in accordance with an embodiment of the present technology. -
FIGS. 17A and 17B are schematic cross-sectional illustrations of the operation of a dynamically-generated vacuum mechanism integrated into the skin-piercing assembly in accordance with an embodiment of the present technology. -
FIGS. 18A and 18B are cross-sectional views of a bodily fluid collection device having a dynamically-generated vacuum mechanism integrated into the skin-piercing assembly and configured in accordance with an embodiment of the present technology. -
FIGS. 19A-19E are schematic cross-sectional illustrations of skin interfaces to control skin curvature in accordance with embodiments of the present technology. -
FIG. 20 is a block diagram of a method for withdrawing bodily fluid from a patient's skin using a flexible membrane in accordance with an embodiment of the present technology. -
FIGS. 21A-21C are cross-sectional and perspective views of the flexible membrane of a bodily fluid collection device in accordance with an embodiment of the present technology. -
FIG. 22 is an exploded view of the flexible membrane configured in accordance with an embodiment of the present technology. -
FIGS. 23A-23E are various views of flexible membranes with different surface features and/or treatments configured in accordance with embodiments of the present technology. -
FIGS. 24A-24F are cross-sectional views of housing features to control flow of bodily fluid along the flexible membrane in accordance with embodiments of the present technology. -
FIGS. 25A-25F are cross-sectional and top views of a wicking element for directing flow of a bodily fluid in accordance with an embodiment of the present technology. - Devices and methods in accordance with the present technology can be configured to deploy a skin-piercing feature toward a patient's skin to withdraw bodily fluid (e.g., blood). In some embodiments, the devices and methods disclosed herein use an actuation mechanism that deploys the skin-piercing feature in response to movement of an actuator. In some embodiments, the devices and methods disclosed herein use a vacuum mechanism configured to dynamically generate a vacuum that is applied to the patient's skin to facilitate collection of the bodily fluid. In some embodiments, the devices and methods disclosed herein use a flexible membrane that interfaces with the patient's skin and/or bodily fluid for more efficient withdrawal of bodily fluid. The devices and methods of the present technology can be used to quickly and easily obtain a volume of bodily fluid sufficient for downstream testing and analysis.
- Specific details of the present technology are described herein with reference to
FIGS. 1A-25F . It should be noted that other embodiments in addition to those disclosed herein are within the scope of the present technology. Further, some embodiments of the present technology can have different configurations, components, and/or procedures than those shown or described herein. Moreover, a person of ordinary skill in the art will understand that some embodiments of the present technology can have configurations, components, and/or procedures in addition to those shown or described herein and that these and other embodiments can be without several of the configurations, components, and/or procedures shown or described herein without deviating from the present technology. - The headings provided herein are for convenience only and should not be construed as limiting the subject matter disclosed.
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FIG. 1A is a perspective view of a bodily fluid collection device 100 (“device 100”) configured in accordance with an embodiment of the present technology. Thedevice 100 can be handheld with a size that is easily grasped and manipulated by one or both of a patient's hands. Such handheld devices advantageously allow a patient to collect a bodily fluid sample (e.g., a blood sample) without assistance from another individual. In some embodiments, the handheld devices of the present technology can be operated by a layperson outside of a medical setting (e.g., at home or in a field clinic) and without aid of a medical professional. - As shown in
FIG. 1A , thedevice 100 includes ahousing 102 and anactuator 104. The actuator 104 (e.g., a button) is movable relative to thehousing 102 to actuate withdrawal of a bodily fluid from the patient. Thehousing 102 is removably coupled to a collection reservoir 200 (e.g., a tube or cartridge) for receiving the bodily fluid withdrawn from the patient. Thereservoir 200 can act as a removable and standardized container for bodily fluid that can be detached and inserted into clinical and laboratory equipment or workflows, e.g., for diagnostics and/or biomarker detection. -
FIG. 1B is a perspective view of the bodilyfluid collection device 100 in use. To collect a bodily fluid sample, thedevice 100 is applied to a patient's body, with the bottom surface of thehousing 102 positioned against theskin 250 and theactuator 104 positioned away from theskin 250. Pressing theactuator 104 deploys a skin-piercing feature (e.g., a lancet, blade, or needle) from within thedevice 100 to pierce theskin 250. Subsequent retraction of theactuator 104 away from the skin creates a vacuum within thedevice 100 that acts against the patient's skin either directly or indirectly. Bodily fluid from the resulting incision is withdrawn into thehousing 102 and collected into thereservoir 200. -
FIG. 1C is a perspective view illustrating detachment of thecollection reservoir 200 from the bodilyfluid collection device 100. Once the desired amount of bodily fluid has been collected into thereservoir 200, thedevice 100 is removed from theskin 250, and thereservoir 200 is detached from thehousing 102. -
FIG. 2A is a schematic cross-sectional illustration of a bodilyfluid collection device 100 configured in accordance with an embodiment the present technology. Thedevice 100 includes thehousing 102, theactuator 104, a skin-piercingassembly 106 located at least partially or completely within thehousing 102, and anopening 108 through thehousing 102. In some embodiments, theopening 108 is formed in abottom surface 110 of thehousing 102 such that theopening 108 is against the skin when thedevice 100 is applied to a patient's body. Theactuator 104 is movable relative to thehousing 102 along adeployment direction 112 and aretraction direction 114. Thedeployment direction 112 can be a downward direction in the orientation ofFIG. 2A , e.g., toward theopening 108, and theretraction direction 114 can be an upward direction, e.g., away from theopening 108. Thedeployment direction 112 is generally toward the skin, while theretraction direction 114 is generally away from the skin. - The skin-piercing
assembly 106 includes at least one skin-piercing feature 116 (e.g., a lancet, blade, or needle) and a biasing member 118 (e.g., a spring) that is coupled to the skin-piercingfeature 116. The biasingmember 118 is configured to drive the skin-piercingfeature 116 along thedeployment direction 112 toward theopening 108. The skin-piercingfeature 116 can be configured to pierce the patient's skin to create an incision from which bodily fluid can be withdrawn. The size of the skin-piercing feature can be varied as desired. For example, a relatively large skin-piercing feature can be advantageous for creating a larger incision that allows for withdrawal of larger volumes of bodily fluid. A relatively small skin-piercing feature can be advantageous for reducing pain and achieving high penetration velocities. Optionally, the skin-piercingassembly 106 can include a plurality of skin-piercing features, e.g., two, three, four, five, or more skin-piercing features. In some embodiments, thedevice 100 can include a corresponding number ofopenings 108, such that each skin-piercing feature passes through a respective opening to pierce the patient's skin. However, more than one skin piercing feature 116 can pass through anopening 108. For example, all of the skin piercing features 116 can pass through asingle opening 108. -
FIG. 2B is a side view of the skin-piercingfeature 116 of thedevice 100 configured in accordance with an embodiment the present technology. The length of the skin-piercingfeature 116 can be selected to produce an appropriate penetration depth into theskin 250. For example, the skin-piercingfeature 116 can have a length of about 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, 3.5 mm, 3.6 mm, 3.7 mm, 3.8 mm, 3.9 mm, or 4.0 mm. The length of the skin-piercingfeature 116 can be selected to produce a penetration depth less than or equal to about 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, 3.5 mm, 3.6 mm, 3.7 mm, 3.8 mm, 3.9 mm, or 4.0 mm below the surface of theskin 250. -
FIG. 2C is a side view of the skin-piercingfeature 116 with astop feature 117 configured in accordance with an embodiment the present technology. In some embodiments, thestop feature 117 is at or near the base of the skin-piercingfeature 116 to limit the penetration depth of the skin-piercingfeature 116 into the skin. For example, thestop feature 117 can limit the penetration depth to less than or equal to about 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1.0 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, 2.0 mm, 2.1 mm, 2.2 mm, 2.3 mm, 2.4 mm, 2.5 mm, 2.6 mm, 2.7 mm, 2.8 mm, 2.9 mm, 3.0 mm, 3.1 mm, 3.2 mm, 3.3 mm, 3.4 mm, 3.5 mm, 3.6 mm, 3.7 mm, 3.8 mm, 3.9 mm, or 4.0 mm below the surface of theskin 250. - Referring back to
FIG. 2A , thedevice 100 includes an actuation mechanism for actuating the deployment of the skin-piercingassembly 106. For example, theactuator 104 can be mechanically coupled to the skin-piercingassembly 106, e.g., via aplatform 120 and aplunger 122, to deploy the skin-piercing feature along thedeployment direction 112. In the depicted embodiment, theplatform 120 is located at least partially within theactuator 104, theplunger 122 is located at least partially within theplatform 120, and the skin-piercingassembly 106 is coupled to theplunger 122. Optionally, the actuation mechanism can also actuate the retraction of the skin-piercingfeature 116 along theretraction direction 114, after the skin-piercingfeature 116 has been deployed. Additional features and implementations of the actuation mechanism are described herein with reference toFIGS. 4-12C . - In some embodiments, the
device 100 includes a vacuum mechanism to facilitate collection of the bodily fluid. For example, thedevice 100 can include a sealing member 124 (e.g., a flexible membrane that can bend and/or is elastic) over theopening 108 to form alumen 126. Thedevice 100 can include at least onevalve 128 fluidically connected to thelumen 126 to control air flow into and out of thelumen 126. The sealingmember 124 can be mechanically coupled to the skin-piercingassembly 106, e.g., via theplunger 122, such that movement of the skin-piercingassembly 106 along thedeployment direction 112 decreases the volume of thelumen 126, and movement of the skin-piercingassembly 106 along theretraction direction 114 increases the volume of thelumen 126. Thevalve 128 can be a one-way valve that permits air to escape from within thelumen 126, e.g., as the lumen volume decreases, but prevents air from entering thelumen 126, e.g., as the lumen volume increases. This creates a low-pressure region (e.g., a vacuum) within thelumen 126 that acts directly or indirectly against the skin. Additional features and implementations of the vacuum mechanism are described herein with reference toFIGS. 13A-18B . - In some embodiments, the
device 100 includes a skin interface that interacts with the patient's skin and/or bodily fluid to facilitate collection of the bodily fluid. The skin interface can control the curvature of the skin to maintain the incision in an open position, thus promoting flow of the bodily fluid from the skin. The skin interface can also include surface features and/or treatments to direct flow of the bodily fluid toward a desired location, e.g., into thehousing 102 and toward the collection reservoir. For example, thedevice 100 can include aflexible membrane 130 coupled to thehousing 102 and covering at least a portion of theopening 108. Theflexible membrane 130 can be bendable and/or stretchable (e.g., elastic). Theflexible membrane 130 can be coupled to thebottom surface 110 of thehousing 102, such that themembrane 130 is on the exterior of thehousing 102. Alternatively, theflexible membrane 130 can be within the interior of thehousing 102. Theflexible membrane 130 can optionally include an aperture to allow the skin-piercingfeature 116 to pass through. Theflexible membrane 130 can be made of an elastic material (e.g., polyurethane, silicone) that deforms into a curved shape when exposed to a vacuum. When thedevice 100 is applied to the patient's body, theflexible membrane 130 can form a seal against the patient's skin to control the skin curvature and/or direct flow of the bodily fluid from the skin. Additional features and implementations of skin interfaces are described herein with reference toFIGS. 19A-25F . -
FIG. 3 is a block diagram of amethod 300 for using a bodily fluid collection device configured in accordance with an embodiment the present technology. Although various steps of themethod 300 are described with respect to the components of thedevice 100, it shall be appreciated that themethod 300 is generally applicable to any embodiment of the bodily fluid collection devices disclosed herein. - The
method 300 includes providing a bodily fluid collection device having a skin-piercing feature (block 310) and deploying the skin-piercing feature toward a patient's skin (block 320). The deployment of the skin-piercing feature can be driven by an actuation mechanism, as described herein with reference toFIGS. 4-12C . In some embodiments, the actuation mechanism includes an actuator mechanically coupled to the skin-piercing assembly, such that movement of the actuator along the deployment direction drives the skin-piercing feature to be deployed toward the opening along the deployment direction. For example, in the embodiment ofFIG. 2A , theactuator 104 engages and moves theplatform 120 along thedeployment direction 112, theplatform 120 engages and moves theplunger 122 along thedeployment direction 112, and the movement of theplunger 122 along thedeployment direction 112 causes the skin-piercingfeature 116 to be deployed. In some embodiments, the movement of theplunger 122 along thedeployment direction 112 releases a load on the biasingmember 118, thus causing the biasingmember 118 to actively drive the skin-piercingfeature 116 along thedeployment direction 112. In some embodiments, the biasingmember 118 is not initially loaded, but movement of theactuator 104,platform 120, andplunger 122 loads the biasingmember 118 with a stored energy until the actuator reaches a trigger point that releases the skin-piercingfeature 116. This allows the stored energy in the biasingmember 118 to be quickly released and thereby drive the skin-piercingfeature 116 at a high velocity into the skin. This approach is expected to allow for easier device assembly, improve device stability and safety, increase device shelf life, and reduce fatigue on the biasing member. - The skin-piercing feature can be deployed at any velocity suitable for creating an incision in the patient's skin for withdrawing bodily fluid. As used herein, “velocity” may refer to a maximum velocity, an average velocity, or a velocity at the time the skin-piercing feature contacts the skin. In some embodiments, the skin-piercing feature is deployed at a velocity greater than or equal to about 0.1 m/s, 0.2 m/s, 0.3 m/s, 0.4 m/s, 0.5 m/s, 0.6 m/s, 0.7 m/s, 0.8 m/s, 0.9 m/s, 1.0 m/s, 1.5 m/s, 2.0 m/s, or 2.5 m/s. In some embodiments, the skin-piercing feature is deployed at a velocity less than or equal to about 0.1 m/s, 0.2 m/s, 0.3 m/s, 0.4 m/s, 0.5 m/s, 0.6 m/s, 0.7 m/s, 0.8 m/s, 0.9 m/s, 1.0 m/s, 1.5 m/s, 2.0 m/s, or 2.5 m/s. In some embodiments, the skin-piercing feature is deployed at a velocity within a range from about 0.1 m/s to about 2.5 m/s.
- In some embodiments, the skin-piercing feature is deployed at a high velocity, e.g., a velocity greater than or equal to about 2.5 m/s. High velocity deployment of the skin-piercing feature can produce more effective penetration for some skin types with low stiffness or elasticity, create a larger incision that permits withdrawal of a larger volume of bodily fluid, or allow the use of the device on other mammalian species other than humans. Alternatively, in some embodiments, the skin-piercing feature is deployed at a low velocity, e.g., a velocity less than or equal to about 0.1 m/s. Low velocity deployment of the skin-piercing feature can reduce the pain experienced by the patient.
- The
method 300 further includes retracting the skin-piercing feature away from the patient's skin (block 330). The skin-piercing feature can be retracted by an actuation mechanism, as described herein with reference toFIGS. 4-12C . The skin-piercing feature can be retracted at least partially or completely into the housing along the retraction direction. In some embodiments, the skin-piercing feature is retracted automatically after deployment such that the patient does not need to perform any additional actions for retraction to occur. Optionally, the skin-piercing feature is locked into the retracted position such that further movement of the actuator along the deployment direction does not re-deploy the skin-piercing feature. - The
method 300 further includes applying a vacuum to the patient's skin (block 340). For example, the device can include a vacuum mechanism that generates the vacuum contemporaneously with the deployment and retraction of the skin-piercing feature, as described herein with reference toFIGS. 13A-18B . For example, in the embodiment ofFIG. 2 , movement of theplunger 122 along thedeployment direction 112 decreases the volume of thelumen 126. Air can escape from within thelumen 126 via thevalve 128 as the volume decreases. When theplunger 122 is moved along theretraction direction 114, the volume of thelumen 126 increases, while thevalve 128 prevents air from entering thelumen 126. Accordingly, the pressure within thelumen 126 decreases, creating a vacuum within thelumen 126 that draws the bodily fluid and/or a portion of the patient's skin through theopening 108. In some embodiments, the valve can be mechanically shutoff as theplunger 122 reaches desired displacement position, such as the further-most displacement position. This is expected to increase the amount of bodily fluid withdrawn from the skin by opening local capillaries and maintaining the incision in an open configuration. - The
method 300 further includes withdrawing bodily fluid into the bodily fluid collection device (block 350). Once the skin-piercing feature has formed an incision in the patient's skin, bodily fluid from the incision is drawn into the housing through the opening and into a collection reservoir. Optionally, the device can include a skin interface (e.g., a flexible membrane) that interacts with the skin and/or bodily fluid to enhance flow of the bodily fluid into the device, as described herein with reference toFIGS. 19A-25F . In some embodiments, a flexible membrane is expected to provide improved control over larger areas of skin, thus allowing the device to access more capillaries and increase the volume of bodily fluid that can be withdrawn, as well as provide a support to collect blood close to the incision point to prevent or at least mitigate the blood from travelling on the skin of the user. This further allows the delivery of anticoagulant material rapidly after the blood is extracted from the capillaries. - The amount of bodily fluid withdrawn into the device, also known as the “draw volume,” can be sufficiently large for downstream testing and analysis of the bodily fluid, e.g., for diagnostics and/or biomarker detection performed on a blood sample. As used herein, draw volume can refer to the maximum volume of bodily fluid that can be collected from a specified percentage of the patient population, e.g., from at least 90% of patients. The draw volume of the device can be at least about 50 μL, 75 μL, 100 μL, 125 μL, 150 μL, 175 μL, 200 μL, 225 μL, 250 μL, 275 μL, 300 μL, 325 μL, 350 μL, 375 μL, 400 μL, 425 μL, 450 μL, 475 μL, 500 μL, 550 μL, 600 μL, 650 μL, 700 μL, 750 μL, 800 μL, 850 μL, 900 μL, 950 μL, 1 mL, 1.5 mL, or 2 mL of the bodily fluid from the patient. In some embodiments, the draw volume of the device is up to about 50 μL, 75 μL, 100 μL, 125 μL, 150 μL, 175 μL, 200 μL, 225 μL, 250 μL, 275 μL, 300 μL, 325 μL, 350 μL, 375 μL, 400 μL, 425 μL, 450 μL, 475 μL, 500 μL, 550 μL, 600 μL, 650 μL, 700 μL, 750 μL, 800 μL, 850 μL, 900 μL, 950 μL, 1 mL, 1.5 mL, or 2 mL of the bodily fluid from the patient. In some embodiments, the draw volume of the device is within a range from about 50 μL to about 2 mL, from about 100 μL to about 2 mL, from about 100 μL to about 1.5 mL, from about 100 μL to about 1 mL, or from about 100 μL to about 500 μL.
- The bodily fluid collection devices of the present technology can include an actuation mechanism that deploys the skin-piercing assembly. In some embodiments, the actuation mechanism includes an actuator that is mechanically coupled to the skin-piercing assembly, such that movement of the actuator causes a skin-piercing feature of the skin-piercing assembly to be deployed along a deployment direction toward the patient's skin. The actuator movement that deploys the skin-piercing feature can be a simple, unidirectional movement that is easily performed by a layperson, such as pressing a button.
- The actuation mechanism can include a biasing member (e.g., a spring) that is coupled to the skin-piercing feature to drive the skin-piercing feature along a deployment direction. The biasing member can have an unloaded state (e.g., an uncompressed state), in which little or no load is placed on the biasing member (e.g., little or no energy is stored in the biasing member), and a loaded state (e.g., a compressed state), in which a load is placed on the biasing member (e.g., sufficient energy to drive the skin-piercing
feature 116 at a desired velocity is stored in the biasing member). When the load on the biasing member is released, the biasing member transitions from the loaded state to the unloaded state, and the transition of the biasing member to the unloaded state drives the deployment of the skin-piercing feature in the deployment direction. - In some embodiments, the actuation mechanism is configured such that moving the actuator along the deployment direction both applies and releases a load on the biasing member (“in situ loaded”). An in situ loaded actuation mechanism may include little or no load on the biasing member before moving the actuator from an initial position along the deployment direction. For example, the load on the biasing member before moving the actuator can be less than or equal to about 15%, 10%, 5%, or 1% of the maximum load on the biasing member during operation of the bodily fluid collection device. As another example, the length of the biasing member before moving the actuator from the initial position can be at least about 85%, 90%, 95%, or 99% of its unloaded length. Advantages of an in situ loaded actuation mechanism include easier device assembly, improved device stability and safety, longer device shelf life, and reduced fatigue on the biasing member.
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FIG. 4 is a block diagram of amethod 400 for deploying a skin-piercing feature using an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology. Themethod 400 can be applied to any of the bodily fluid collection devices disclosed herein, such as thedevice 100. Additionally, one or more steps of themethod 400 can be combined with or substituted for any of the steps of the other methods disclosed herein. For example, one or more steps of themethod 400 can be performed in combination with or as sub-steps ofblock 320 of themethod 300. - The
method 400 includes moving an actuator to a predetermined position (block 410). The predetermined position can be a position along a deployment direction (e.g., toward the patient's skin). For example, a patient can press the actuator once the bodily fluid collection device has been applied to the skin. In some embodiments, the predetermined position is at least about 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 4.5 mm, 5 mm, 5.5 mm, 6 mm, 6.5 mm, 7 mm, 7.5 mm, 8 mm, 8.5 mm, 9 mm, 9.5 mm, 10 mm, 15 mm, or 20 mm from an initial resting position of the actuator. - The method further includes applying a load to a biasing member coupled to a skin-piercing feature (block 420). The load can be applied to the biasing member by the movement of the actuator along the deployment direction to the predetermined position. The biasing member can initially be in an unloaded state with little or no applied load, and moving the actuator can increase the load on the biasing member to at least a partially loaded state, or to a fully loaded state. In some embodiments, the actuator is mechanically coupled to the biasing member to apply the load on the biasing member, e.g., by compressing the biasing member. For example, the biasing member can be compressed to a loaded length that is less than or equal to about 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, or 85% of its unloaded length.
- The method next includes moving the actuator beyond the predetermined position (block 430). For example, the actuator can be moved to a position that is further along the deployment direction than the predetermined position, e.g., by the patient continuing to press on the actuator while the device is applied to the skin. In some embodiments, the actuator is moved beyond the predetermined position by a distance of at least about 0.1 mm, 0.5 mm, 1 mm, 1.5 mm, 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 4.5 mm, or 5 mm.
- The method also includes releasing the load on the biasing member (block 440). The load can be released by moving the actuator along the deployment direction beyond the predetermined position. The method further includes driving the skin-piercing feature toward a patient's skin (block 450). The skin-piercing feature can be collectively driven toward the patient's skin by both the actuator and the biasing member. In some embodiments, moving the actuator along the deployment direction beyond the predetermined position releases the load on the biasing member so that the biasing member actively drives the skin-piercing feature along the deployment direction. For example, the biasing member can drive the skin-piercing feature as the biasing member extends from a compressed state toward an uncompressed state.
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FIGS. 5A-5C are schematic cross-sectional illustrations of the operation of an in situ loadedactuation mechanism 500 configured in accordance with an embodiment the present technology. Theactuation mechanism 500 includes the biasingmember 118, theplunger 122, thehousing 102, and the actuator (not shown). The skin-piercingfeature 116 is coupled to the biasingmember 118 via abase 502. Theplunger 122 is positioned around at least a portion of the skin-piercingassembly 106 and includes one ormore projections 504. Thehousing 102 includes theopening 108 and one ormore arms 506 within thehousing 102. - Before moving the actuator along the deployment direction (
FIG. 5A ), there is little or no loading on the biasingmember 118, such that the biasing member is at or near its uncompressed length. Moving the actuator along the deployment direction up to a predetermined position (FIG. 5B ) causes the arm(s) 506 to assume a flexed configuration that engages thebase 502 and applies a load to the biasingmember 118. For example, in the depicted embodiment, the actuator engages and moves theplunger 122 and skin-piercingassembly 106 downward toward theopening 108. This downward movement brings the arm(s) 506 into engagement with thebase 502. The arm(s) 506 are in a flexed configuration (e.g., inwardly bent configuration) that presses up against thebase 502, causing the biasingmember 118 to be compressed between the base 502 and theplunger 122. - Moving the actuator along the deployment direction beyond the predetermined position (
FIG. 5C ) causes the arm(s) 506 to flex outward and thereby disengaged from the base 502 (e.g., a resting configuration or release configuration), which in turn releases the load on the biasingmember 118. For example, in the depicted embodiment, continued downward movement of the actuator brings the projection(s) 504 of theplunger 122 into contact with the inwardly flexed arm(s) 506. Eachprojection 504 contacts and displaces acorresponding arm 506 from the inwardly flexed configuration to a released configuration, e.g., by bending thearm 506 outward. Once in the released configuration, the arm(s) 506 disengage from thebase 502 and release the compression on the biasingmember 118. The biasingmember 118 reverts toward its uncompressed length, driving the skin-piercingfeature 116 downward toward theopening 108. - The features of the
actuation mechanism 500 can be varied as desired. For example, althoughFIGS. 5A-5C illustrate amechanism 500 with two projections and two arms, alternative embodiments may include any suitable number of projections and arms. In some embodiments, themechanism 500 can include one, two, three, four, five, or more projections; and one, two, three, four, five, or more arms. The positioning of the projection(s) 504 and the arm(s) 506 can also be varied. For instance, the projection(s) 504 can be on thehousing 102, and the arm(s) 506 can be on theplunger 122. Additionally, althoughFIGS. 5A-5C illustrate the arm(s) 506 being displaced outward by the projection(s) 504 to release the biasingmember 118, in alternative embodiments, the arm(s) 506 may be displaced inward by the projection(s) 504 to release the biasingmember 118. -
FIGS. 6A-10 illustrate a bodilyfluid collection device 100 with an in situ loaded actuation mechanism configured in accordance with an embodiment the present technology. Thedevice 100 includes thehousing 102, theactuator 104, and the skin-piercingassembly 106. Thehousing 102 includes anupper housing portion 602A and alower housing portion 602B. In some embodiments, theupper housing portion 602A and thelower housing portion 602B are separate components that are coupled together to form thehousing 102. In alternative embodiments, theupper housing portion 602A andlower housing portion 602B can be integrally formed as a single unitary component. Theupper housing portion 602A is shaped to receive theactuator 104. Thelower housing portion 602B includes thebottom surface 110 having theopening 108. - The
actuator 104 is at least partially within theupper housing portion 602A of thedevice 100. In some embodiments, theactuator 104 is a hollow, button-like structure positioned to be depressed by the patient along thedeployment direction 112 to deploy the skin-piercingfeature 116 of the skin-piercingassembly 106. Theactuator 104 can be mechanically coupled to the skin-piercingassembly 106 via one or more internal device components, such as theplatform 120,washer 604, sealingmember 124, and/orplunger 122. In some embodiments, theactuator 104 is positioned around at least a portion of theplatform 120, theplatform 120 is positioned around at least a portion of thewasher 604, and thewasher 604 is positioned around at least a portion of the sealingmember 124, and the sealingmember 124 is positioned around at least a portion of theplunger 122. Theactuator 104,platform 120,washer 604, sealingmember 124, andplunger 122 can be concentrically positioned, such that the longitudinal axes (e.g., the axis extending along the deployment direction 112) of these components are aligned. - The
actuator 104,platform 120,washer 604, sealingmember 124, andplunger 122 can be coupled to each other using any suitable combination of complementary interconnecting features (e.g., notches, grooves, projections, tabs, and the like). In some embodiments, thelower edge 606 of theactuator 104 engages at least onetab feature 608 of theplatform 120 when theactuator 104 is moved along thedeployment direction 112. The at least onetab feature 608 can extend radially outward from an outer surface of theplatform 120 to receive and engage thelower edge 606 of theactuator 104. In some embodiments, theplatform 120 includes at least one projectingfeature 610 that engages at least onetab feature 612 of thewasher 604 when theplatform 120 is moved along thedeployment direction 112. The at least one projectingfeature 610 can extend radially inward from an inner surface of theplatform 120, and the at least onetab feature 612 can extend radially outward from an outer surface of thewasher 604. Optionally, thewasher 604 can include three tab features evenly spaced along the outer surface of thewasher 604, as shown inFIGS. 6C-6D . In some embodiments, thelower edge 614 of thewasher 604 engages the sealingmember 124 and acollar feature 616 of theplunger 122 when thewasher 604 is moved along thedeployment direction 112. Thecollar feature 616 can extend radially outward from an outer surface of theplunger 122 to receive and engage thelower edge 614 of thewasher 604. - Although the
actuator 104,platform 120,washer 604, sealingmember 124, andplunger 122 are depicted inFIGS. 6A-6E as being separate components, one or more of these components may also be integrally formed with each other. For example, the sealingmember 124 and theplunger 122 can be integrally formed as a single unitary component, e.g., by overmolding. As another example, thewasher 604, sealingmember 124, andplunger 122 can be integrally formed as a single unitary component, e.g., by overmolding. Such approaches may be beneficial for reducing the number of components to simplify device assembly. - The skin-piercing
assembly 106 is mechanically coupled to theplunger 122. In some embodiments, the skin-piercingassembly 106 is coupled to an interior surface of theplunger 122, such that theplunger 122 is around at least a portion of the skin-piercing assembly. The skin-piercingassembly 106 can include the biasingmember 118,base 502, and at least one skin-piercingfeature 116. The biasingmember 118 can have an upper portion coupled to the interior surface of theplunger 122 and a lower portion coupled to thebase 502. The skin-piercingfeature 116 can be mounted to thebase 502. - The
device 100 includes at least onearm 506 within thehousing 102 near theopening 108. Thearm 506 can be integrally formed with the lower housing portion 502B, or can be a separate component that is coupled to the lower housing portion 502B. Thearm 506 can be a flexible component that is movable between a flexed configuration (e.g., an inwardly bent configuration) and a resting configuration (e.g., a straightened or outwardly bent configuration). -
FIG. 6A is a cross-sectional view of thedevice 100 prior to movement of theactuator 104 along the deployment direction 112 (“pre-actuation state”). In the pre-actuation state, thearm 506 is initially in a flexed configuration engaging thebase 502. The base 502 can include ahook feature 618 that receives theend portion 620 of thearm 506. Thehook feature 618 can restrain thearm 506 in the flexed configuration and prevent thearm 506 from reverting to the released configuration. When theactuator 104 is moved along thedeployment direction 112 up to a predetermined position (“actuation state”), the platform, 120,washer 604, sealingmember 124, andplunger 122 are also moved along thedeployment direction 112 by engagement of their respective interconnecting features, as discussed above. Accordingly, thearm 506 compresses the biasingmember 118 between the base 502 and theplunger 122, thus applying a load to the biasingmember 118. -
FIG. 7 is a cross-sectional view of thedevice 100 when theactuator 104 is moved beyond the predetermined position (“deployment state”), andFIG. 8 is a cross-sectional view of thedevice 100 when theactuator 104 is at the maximum position along the deployment direction 112 (“peak deployment state”). As theactuator 104 moves beyond the predetermined position, theplunger 122 moves toward thearm 506 until theend portion 620 of thearm 506 contacts at least oneprojection 504 within theplunger 122. The base 502 can include a notch formed in thehook feature 618 to permit contact between theend portion 620 of thearm 506 and theprojection 504. Theprojection 504 includes aninclined surface 622 that contacts and displaces thearm 506 outward from thehook feature 618 so that thearm 506 moves from the flexed configuration to the released configuration. In the released configuration, thearm 506 disengages from thebase 502 and deflects outward into achannel 624 formed between theprojection 504 and asidewall 626 of theplunger 122. - Once the
arm 506 disengages thebase 502, the load on the biasingmember 118 is released (e.g., the stored energy is released), causing the biasingmember 118 to drive thebase 502 and the skin-piercingfeature 116 toward theopening 108. Theplunger 122 can optionally include alatch portion 628 to restrict the movement of the skin-piercingfeature 116 along thedeployment direction 112. In some embodiments, the latch portion engages acomplementary stop feature 630 on the base 502 to stop the movement of thebase 502 and skin-piercingfeature 116 along thedeployment direction 112. Thelatch portion 628 can be positioned away from theupper portion 632 of theplunger 122, with the distance from theupper portion 632 and thelatch portion 628 being configured to permit the skin-piercingfeature 116 to attain a desired penetration velocity. For example, the distance can be at least about 1 mm, 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, or 10 mm. In some embodiments, the distance can be within a range from about 4 mm to about 8 mm. -
FIG. 9 is a cross-sectional view of thedevice 100 after retraction of the skin-piercing feature 116 (“retraction state”). In some embodiments, the actuation mechanism of thedevice 100 also automatically retracts the skin-piercingfeature 116 after deployment without requiring any additional actuation of the device components by the patient. For example, thedevice 100 can include a second biasing member 634 (e.g., a spring) configured to bias the skin-piercingfeature 116 along theretraction direction 114 away from theopening 108. Thesecond biasing member 634 can have an unloaded state (e.g., an uncompressed state) in which little or no load is placed on thesecond biasing member 634, and a loaded state (e.g., a compressed state) in which a load is placed on thesecond biasing member 634. When the load on thesecond biasing member 634 is released, thesecond biasing member 634 moves from the loaded state toward the unloaded state, and the movement of thesecond biasing member 634 toward the unloaded state drives the retraction of the skin-piercingfeature 116. - The second biasing member can be coupled between the actuator 104 and the
lower housing portion 602B. As shown inFIGS. 7 and 8 , movement of theactuator 104 along the deployment direction compresses thesecond biasing member 634, thus applying a load to thesecond biasing member 634 causing energy to be stored in thesecond biasing member 634. When the patient or user stops pushing on theactuator 104, the load on thesecond biasing member 634 is released, causing thesecond biasing member 634 to drive theactuator 104 along theretraction direction 114. Movement of theactuator 104 along theretraction direction 114 also moves theplatform 120,washer 604, sealingmember 124, andplunger 122 along theretraction direction 114 by engagement of their respective interconnecting features, as discussed above. Movement of theplunger 122 along theretraction direction 114 also retracts the biasingmember 118,base 502, and skin-piercingfeature 116 along theretraction direction 114 away from theopening 108. As thesecond biasing member 634 moves theplatform 120,plunger 122 and sealingmember 124 in theretraction direction 114, the volume within the sealingmember 124 increases causing a decrease in pressure (e.g., a vacuum) within the volume bounded by the sealingmember 124 that draws blood from the patient. -
FIG. 10 is a cross-sectional view of thedevice 100 when theactuator 104 is moved along thedeployment direction 112 after retraction of the skin-piercing feature 116 (“re-actuation state”). Thedevice 100 can include a locking mechanism configured to prevent re-deployment of the skin-piercingfeature 116 after the skin-piercingfeature 116 has already been retracted. Accordingly, even if the patient presses theactuator 104 again, the skin-piercingfeature 116 is retained within thehousing 102 and does not deploy. Additional features and implementations of the locking mechanism are described herein with reference toFIGS. 12A-12C . - In some embodiments, the bodily fluid collection devices of the present technology include an actuation mechanism in which the biasing member driving the deployment of the skin-piercing features is partially or fully loaded prior to movement of the actuator (“pre-loaded”). Accordingly, movement of the actuator along the deployment direction simply releases the load on the biasing member, with little or no additional loading applied.
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FIGS. 11A-11H are schematic top and cross-sectional illustrations of the operation of a pre-loaded actuation mechanism configured in accordance with an embodiment the present technology. The actuation mechanism includes a deployment assembly 1100 (FIGS. 11A-11D ) and a retraction assembly 1150 (FIGS. 11E-11G ). As shown inFIG. 11A (top view) and 11B (cross-sectional view), thedeployment assembly 1100 includes aplate 1102, anaperture 1104 in theplate 1102, and ashaft 1106 extending through theaperture 1104. Theshaft 1106 includes anupper end portion 1108A and alower end portion 1108B. Theupper end portion 1108A is coupled to at least onestop feature 1110 having a shape complementary to the shape of theaperture 1104. For example, thestop feature 1110 can include one or more tabs protruding radially outward from theshaft 1106, and theaperture 1104 can include one or more recesses shaped to receive the one more tabs. Thelower end portion 1108B is coupled to the base 502 carrying the skin-piercingfeature 116. The biasingmember 118 is positioned at least partially around theshaft 1106 between the lower surface of theplate 1102 and the upper surface of thebase 502. - As shown in
FIGS. 11A and 11B , prior to actuation of the bodily fluid collection device, thestop feature 1110 is oriented on the upper surface of theplate 1102 such that thestop feature 1110 is not aligned with theaperture 1104. For example, thestop feature 1110 can be rotated relative to theaperture 1104 such that the protrusions of thestop feature 1110 are not over the corresponding recesses of theaperture 1104, and are instead against the upper surface of theplate 1102. Accordingly, thestop feature 1110 prevents movement of theshaft 1106,base 502, and skin-piercingfeature 116 toward the deployment direction. The length of theshaft 1106 can be selected such that the biasingmember 118 is held between the base 502 andplate 1102 in at least a partially loaded state. For example, the biasingmember 118 can be held at a loaded length that is less than or equal to about 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, or 85% of its unloaded length. - During actuation of the bodily fluid collection device, movement of the actuator along the deployment direction causes a rotational movement of the
stop feature 1110, e.g., along arotational direction 1112. Therotational direction 1112 can be a clockwise direction or a counterclockwise direction. As shown inFIG. 11C (top view) and 11D (cross-sectional view), the rotational movement brings thestop feature 1110 into alignment with theaperture 1104 such that thestop feature 1110 can pass through theaperture 1104. For example, thestop feature 1110 can be rotated such that the protrusions of thestop feature 1110 are over the corresponding recesses of theaperture 1104. The alignment of thestop feature 1110 with theaperture 1104 releases the load on the biasingmember 118. Without thestop feature 1110 restraining the biasingmember 118 to its loaded length, the biasingmember 118 can extend toward its unloaded length, thus driving thebase 502 and skin-piercingfeature 116 along thedeployment direction 112 toward the patient's skin. - The
retraction assembly 1150 can be used in combination with thedeployment assembly 1100 to retract the skin-piercingfeature 116 after deployment. For example, theretraction assembly 1150 can be around at least a portion of thedeployment assembly 1100 and/or the skin-piercingfeature 116. As shown inFIG. 11E (top view) and 11F (cross-sectional view), theretraction assembly 1150 includes acap 1152 having anouter surface 1154A and aninner surface 1154B. Thecap 1152 includes one ormore protrusions 1156 extending radially outward from theouter surface 1154A. Thesecond biasing member 634 is received within agroove 1158 formed in theinner surface 1154B of thecap 1152. Thesecond biasing member 634 is coupled between aninner collar 1160 of thecap 1152 and thehousing 102 of the device. Theretraction assembly 1150 further includes one or more latch features 1162 extending radially inward toward thecap 1152. The latch features 1162 can be on a portion of the device that is stationary relative to the skin-piercingfeature 116, such as thehousing 102. - As shown in
FIGS. 11E and 11F , prior to deployment of the skin-piercingfeature 116, thecap 1152 can be oriented such that theprotrusions 1156 are aligned with the latch features 1162. The latch features 1162 can engage theprotrusions 1156 such that thecap 1152 is held in place relative to thehousing 102. The height of thegroove 1158 within thecap 1152 can be selected such that thesecond biasing member 634 is held between theinner collar 1160 and thehousing 102 in at least a partially loaded state. For example, thesecond biasing member 634 can be held at a loaded length that is less than or equal to about 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, or 85% of its unloaded length. - The deployment of the skin-piercing feature causes a rotational movement of the
cap 1152, e.g., along arotational direction 1164. Therotational direction 1164 can be a clockwise direction or a counterclockwise direction. As shown inFIG. 11G (top view) andFIG. 11H (cross-sectional view), the rotational movement brings the latch features 1162 out of alignment with theprotrusions 1156, thus releasing the load on thesecond biasing member 634. Thesecond biasing member 634 can extend toward its unloaded length, thus driving thecap 1152 along theretraction direction 114. Thecap 1152 can be mechanically coupled to the skin-piercingfeature 116 such that movement of thesecond biasing member 634 toward its unloaded length moves the skin-piercingfeature 116 along theretraction direction 114 away from the patient's skin. - The features of the
deployment assembly 1100 and theretraction assembly 1150 can be varied as desired. For example, various numbers, sizes, and/or shapes of thestop feature 1110 and/oraperture 1104 can be used. In some embodiments, thestop feature 1110 includes one, two, three, four, five, or more tabs; and theaperture 1104 includes one, two, three, four, five, or more corresponding recesses. As another example, the number, size, and/or shape of theprotrusions 1156 and/or latch features 1162 can be varied as desired. For example, theretraction assembly 1150 can include one, two, three, four, five, or more protrusions; and one, two, three, four, five, or more latch features. - The bodily fluid collection devices of the present technology can include a locking mechanism configured to prevent re-deployment of a skin-piercing feature after the skin-piercing feature has been deployed and retracted into the device. The locking mechanism is expected to improve safety by making the device single-use only, thus reducing the risk of injury or accidental reuse of a contaminated device. In some embodiments, the locking mechanism includes a switchable feature that is movable between a pre-retraction configuration and a post-retraction configuration. The switchable feature can initially be in the pre-retraction configuration, and can be moved into the post-retraction configuration with the retraction of the skin-piercing feature. In the post-retraction configuration, the switchable feature can constrain the movement of one or more device components (e.g., the actuator, plunger, skin-piercing assembly) to prevent the skin-piercing feature from being re-deployed even if the actuator is moved along the deployment direction. For example, the switchable feature can constrain the one or more device components to move along a movement path that is different from a pre-retraction movement path and does not permit the skin-piercing feature to re-deploy.
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FIGS. 12A-12C are schematic cross-sectional illustrations of the operation of alocking mechanism 1200 configured in accordance with an embodiment the present technology. Thelocking mechanism 1200 can be incorporated into any embodiment of the bodily fluid collection devices disclosed herein. For example, thelocking mechanism 1200 can be incorporated into thedevice 100 ofFIGS. 6A-10 . As another example, thelocking mechanism 1200 can be used in combination with the actuation mechanism ofFIGS. 11A-11H . - The
locking mechanism 1200 includes one or moreswitchable features 1202 and one or more guide features 1204. The switchable features 1202 are on a component that is mechanically coupled to the skin-piercingfeature 116, such as aring 122′ or the actuator 104 (not shown). The guide features 1204 can be on a component of the device that remains stationary relative to the skin-piercingfeature 116, such as the housing 102 (not shown). - The switchable features 1202 are movable between a pre-retraction configuration and a post-retraction configuration. As shown in
FIG. 12A , prior to movement of the actuator along thedeployment direction 112, the switchable features 1202 are initially in the pre-retraction configuration with theircontact portions 1206 along afirst surface 1208A of the guide features 1204. For example, in the pre-retraction configuration, the switchable features 1202 can be bent radially outward with thecontact portions 1206 along an outer surface of the guide features 1204. Thefirst surface 1208A applies a load to thecontact portions 1206 to maintain the switchable features 1202 in the pre-retraction configuration and prevent theswitchable feature 1202 from reverting to the post-retraction configuration. - As shown in
FIG. 12B , as thering 122′ moves along thedeployment direction 112 during deployment of the skin-piercingfeature 116, thecontact portions 1206 of the switchable features 1202 slide along thedeployment direction 112 against thefirst surface 1208A until they reach theend portions 1210 of the guide features 1204, releasing the load on thecontact portions 1206 and allowing the switchable features 1202 to revert to the post-retraction configuration. The movement of the switchable features 1202 to the post-retraction configuration can include linear, radial, and/or rotational movements. In some embodiments, the movement of the switchable features 1202 only includes linear and/or radial movements and does not involve any rotational movements. For example, in the post-retraction configuration, the switchable features 1202 can be bent radially inward. - As shown in
FIG. 12C , when thering 122′ moves along theretraction direction 114 during the retraction of the skin-piercingfeature 116, thecontact portions 1206 of the switchable features 1202 slide along theretraction direction 114 against asecond surface 1208B of the guide features 1204. Thesecond surface 1208B can be an inner surface of the guide features 1204. The switchable features 1202 can be biased toward the post-retraction configuration, such that the switchable features 1202 do not revert to the pre-retraction configuration even if thering 122′ subsequently moves along thedeployment direction 112. The post-retraction configuration of the switchable features 1202 can constrain the movement of thering 122′ to a movement path that prevents the skin-piercingfeature 116 from being re-deployed. For example, thering 122′ can be disengaged from one or more device components (e.g., actuator, platform, collar, skin-piercing assembly) involved in deployment of the skin-piercingfeature 116 while thering 122′ moves along the movement path. - The features of the
locking mechanism 1200 can be varied as desired. For example, althoughFIGS. 12A-12C illustrate amechanism 1200 with two switchable features and two guide features, alternative embodiments may include any suitable number of switchable features and guide features. In some embodiments, themechanism 1200 can include one, two, three, four, five, or more switchable features; and one, two, three, four, five, or more guide features. The positioning of the switchable features and guide features can also be varied. For instance, the switchable features 1202 can be on the actuator, platform, collar, plunger, and/or skin-piercing assembly. The positioning of the switchable features 1202 and the guide features 1204 can also be reversed, such that the switchable features 1202 are on a component that remain stationary relative to the skin-piercingfeature 116, and the guide features 1204 are on a component that moves along with the skin-piercingfeature 116. Additionally, althoughFIGS. 12A-12C illustrate thecontact portions 1206 of the switchable features 1202 being bent outward in the pre-retraction configuration and bent inward in the post-retraction configuration, in alternative implementations, thecontact portions 1206 can be bent inward in the pre-retraction configuration and bent outward in the post-retraction configuration. - The bodily fluid collection devices of the present technology can include a vacuum mechanism configured to apply a vacuum to the patient's skin to facilitate withdrawal of larger volumes of bodily fluid. In some embodiments, the vacuum deforms the skin into a curved shape that opens the capillaries within the skin to increase the local flow of bodily fluid, and also maintains the incision in an opened configuration to promote withdrawal of bodily fluid into the device. For example, the vacuum can be applied by expanding the volume within a flexible membrane, such as the sealing
member 124 described above, as opposed to actively drawing air out of a rigid cup (e.g., withdrawing air from a suction cup.) The timing of vacuum application relative to the other steps in the operation of the bodily fluid collection device can be varied as desired. For example, the vacuum can be applied prior to, concurrently with, and/or after the deployment of the skin-piercing feature to pierce the skin. As another example, the vacuum can be applied prior to, concurrently with, and/or after the retraction of the skin-piercing feature away from the skin. The vacuum mechanisms of the present technology can be used in combination with any of the actuation mechanisms disclosed herein, such as the actuation mechanisms described with reference toFIGS. 4-12C . -
FIGS. 13A-13D , for example, are schematic cross-sectional illustrations of a vacuum being applied to a patient'sskin 250 configured in accordance with an embodiment the present technology. The device is initially applied to the patient's body with thehousing 102 andopening 108 against the skin 250 (FIG. 13A ). A vacuum is applied to theskin 250 to pull at least a portion of theskin 250 into a curved shape (FIG. 13B ). Theskin 250 can be pulled at least partially into the device, such as being pulled at least partially through theopening 108 and into the interior of the housing. While theskin 250 is under vacuum, a skin-piercingfeature 116 is deployed and pierces theskin 250 to create an incision 1300 (FIG. 13C ). The skin-piercingfeature 116 can be then retracted to permit bodily fluid to flow from theincision 1300 into the housing 102 (FIG. 13D ). -
FIGS. 14A-14C are schematic cross-sectional illustrations of a vacuum being applied to a patient'sskin 250 configured in accordance with an embodiment the present technology. The device is initially applied to the patient's body with thehousing 102 andopening 108 against the skin 250 (FIG. 14A ). A vacuum is applied to theskin 250 to pull at least a portion of theskin 250 into a curved shape (FIG. 14B ). Theskin 250 can be pulled at least partially into the device, such as through theopening 108 and into the interior of thehousing 102, and the skin-piercingfeature 116 can pierce theskin 250 to create anincision 1300. In some embodiments, the skin-piercingfeature 116 is held stationary as theskin 250 is pulled into contact with the skin-piercingfeature 116. Alternatively, the skin-piercingfeature 116 can be concurrently deployed toward theskin 250 as the vacuum is applied. The skin-piercingfeature 116 can then be retracted to permit bodily fluid to flow from theincision 1300 into the housing 102 (FIG. 14C ). - In some embodiments, the bodily fluid collection device does not include a pre-existing vacuum source. Instead, the device includes a vacuum mechanism that generates a vacuum along with the deployment and/or retraction of the skin-piercing feature (“dynamically-generated vacuum”). For example, the vacuum mechanism can include a lumen that is initially at or near atmospheric pressure (e.g., gauge pressure is about 0 kPa). When the device is actuated (e.g., during deployment and/or retraction of skin-piercing feature), the vacuum mechanism can lower the pressure within the lumen to less than atmospheric pressure by expanding the volume of the lumen as opposed to withdrawing gas from the lumen, thereby creating a vacuum within the lumen. For example, the lumen can be at a gauge pressure less than or equal to about −10 kPa, −15 kPa, −20 kPa, −25 kPa, −30 kPa, −35 kPa, −40 kPa, −45 kPa, −50 kPa, −55 kPa, or −60 kPa. The lumen can be in fluidic connection with the skin, or a device component that contacts the skin (e.g., the flexible membrane), to apply the vacuum directly or indirectly to the skin.
- In some embodiments, the lumen is mechanically coupled to one or more movable components of the bodily fluid collection device, such that movement of the component along the deployment direction decreases the volume of the lumen, and movement of the component along the retraction increases the volume of the lumen. For example, the lumen can be at least partially formed from a sealing member (e.g., a flexible membrane) that is deformable to increase or decrease the volume of the lumen. In another example, the lumen can be formed from 2 solid cylinders in contact that are able to slide one relative to the other. The vacuum mechanism can further include at least one valve fluidically connected to the lumen to control air flow into and out of the lumen. The valve can be a one-way valve (e.g., a check valve) that permits air to escape from within the lumen as the lumen volume decreases, but prevents air from entering the lumen as the lumen volume increases to dynamically generate a vacuum within the lumen. In other embodiments, the valve can be mechanically shut as the actuation mechanism reaches a predetermined position prior or at the same time as full actuation.
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FIGS. 15A-15C are schematic cross-sectional illustrations of the operation of a dynamically-generatedvacuum mechanism 1500 configured in accordance with an embodiment the present technology. Thevacuum mechanism 1500 includes the sealingmember 124, which is at least partially over theopening 108 in thehousing 102 of the bodily fluid collection device. The sealingmember 124 has anouter portion 1502A and aninner portion 1502B. Theouter portion 1502A of the sealingmember 124 is connected to thehousing 102, and theinner portion 1502B of the sealingmember 124 is connected to theplunger 122, thus a forming alumen 126 in fluidic connection with theopening 108. Theplunger 122 includes the valve 128 (e.g., an umbrella valve) in fluidic connection with thelumen 126. Theplunger 122 can be connected to the skin-piercing assembly 106 (not shown), as described herein. - The device is initially applied to the patient's body with the
opening 108 against the patient's skin, such that thelumen 126 is sealed between the sealingmember 124,plunger 122,housing 102, and the skin. Prior to movement of the actuator of the device (FIG. 15A ), the pressure within thelumen 126 is at or near atmospheric pressure, and thevalve 128 is closed. When the actuator is moved along the deployment direction (e.g., to deploy the skin-piercing feature), theplunger 122 also moves along the deployment direction toward theopening 108, thus reducing the volume of the lumen 126 (FIG. 15B ). The reduction in volume produces a corresponding increase in the pressure within thelumen 126, causing thevalve 128 to open and permit air to escape from within thelumen 126. For example, thevalve 128 can be configured to open when the gauge pressure within the lumen is greater than or equal to about 0.1 kPa, 0.2 kPa, 0.3 kPa, 0.4 kPa, 0.5 kPa, 0.6 kPa, 0.7 kPa, 0.8 kPa, 0.9 kPa, 1.0 kPa, 1.5 kPa, 2 kPa, 2.5 kPa, 3.0 kPa, or 4 kPa. - When the
plunger 122 moves along the retraction direction away from the opening (e.g., when the skin-piercing feature is retracted), the volume of thelumen 126 increases (FIG. 15C ). Thevalve 128 prevents air from entering thelumen 126 as the volume increases, thus producing a corresponding decrease in pressure within thelumen 126. The decreased pressure produces a vacuum that pulls the patient's skin at least partially into the device (e.g., pulls the skin at least partially through theopening 108 and into the lumen 126). - Referring back to
FIGS. 6A-9 , the bodilyfluid collection device 100 can include a dynamically-generated vacuum mechanism configured in accordance with an embodiment the present technology. In some embodiments, the vacuum mechanism includes the sealingmember 124. The sealingmember 124 is coupled to thehousing 102 andplunger 122 to define thelumen 126. The sealingmember 124 can be movable between a collapsed configuration in which the volume of thelumen 126 is decreased, and an extended configuration in which the volume of thelumen 126 is increased. In some embodiments, the sealingmember 124 is mechanically coupled to theplunger 122 so that the movement of theplunger 122 also moves the sealingmember 124 between the collapsed and extended configurations. - The sealing
member 124,housing 102, andplunger 122 can be connected to each other via airtight connections to allow for creation of a low-pressure region (e.g., a vacuum) within thelumen 126. In some embodiments, theouter portion 1502A of the sealingmember 124 is coupled between thehousing 102 and a retainingelement 640. The retainingelement 640 can be a ring-like structure that compresses theouter portion 1502A against acylindrical portion 642 of thehousing 102 to create an airtight connection between the sealingmember 124 and thehousing 102. Theinner portion 1502B of the sealingmember 124 is connected to the upper surface of theplunger 122. The valve 128 (e.g., an umbrella valve) extends through the upper surface of theplunger 122 to control air flow into and out of thelumen 126. - Prior to movement of the actuator of the device (
FIG. 6A ), the pressure within thelumen 126 is at or near atmospheric pressure, and thevalve 128 is closed. During deployment of the skin-piercing feature 116 (FIGS. 7 and 8 ), theplunger 122 moves along thedeployment direction 112, thus moving the sealingmember 124 into the collapsed configuration and reducing the volume of thelumen 126. The reduction in volume produces a corresponding increase in the pressure within thelumen 126, causing thevalve 128 to open and permit air to escape from within thelumen 126. - During retraction of the skin-piercing feature 116 (
FIG. 9 ), theplunger 122 moves along theretraction direction 114, thus pulling the sealingmember 124 into the extended configuration and increasing the volume of thelumen 126. Thevalve 128 prevents air from entering thelumen 126 as the volume increases, thus producing a corresponding decrease in pressure within thelumen 126. The decreased pressure produces a vacuum that pulls the patient's skin at least partially through theopening 108 and into thelumen 126. -
FIGS. 16A-16C are schematic cross-sectional illustrations of the operation of another dynamically-generatedvacuum mechanism 1600 configured in accordance with an embodiment the present technology. Thevacuum mechanism 1600 includes the sealingmember 124 connected to thehousing 102 and theplunger 122 to form thelumen 126. Thelumen 126 is in fluidic connection with one ormore openings 108 in thehousing 102. Theplunger 122 includes thevalve 128 in fluidic connection with thelumen 126. Thehousing 102 includes aprong 1602 extending into thelumen 126 toward thevalve 128. Thevalve 128 can be a mechanically actuated valve that is opened and/or closed by engagement with theprong 1602. - The device is initially applied to the patient's body with the
opening 108 against the patient's skin, such that thelumen 126 is sealed between the sealingmember 124,plunger 122,housing 102, and the skin. Prior to movement of the actuator of the device (FIG. 16A ), the pressure within thelumen 126 is at or near atmospheric pressure, and thevalve 128 is closed. When the actuator is moved along the deployment direction (e.g., to deploy the skin-piercing feature), theplunger 122 also moves along the deployment direction toward theopening 108, thus bringing theprong 1602 in contact with the valve 128 (FIG. 16B ). Theprong 1602 can engage and open thevalve 128 to permit air to escape from within thelumen 126. - When the
plunger 122 moves along the retraction direction away from the opening (e.g., when the skin-piercing feature is retracted), theprong 1602 is disengaged from the valve 128 (FIG. 16C ). Theprong 1602 can close thevalve 128 as it disengages from thevalve 128, thus preventing air from entering thelumen 126. Accordingly, as the volume of thelumen 126 increases, the pressure within thelumen 126 decreases, producing a vacuum that pulls the patient's skin at least partially through theopenings 108 and into thelumen 126. -
FIGS. 17A and 17B are schematic cross-sectional illustrations of the operation of a dynamically-generatedvacuum mechanism 1700 integrated into the skin-piercingassembly 106 configured in accordance with an embodiment the present technology. In themechanism 1700, the skin-piercingassembly 106 itself forms part of thevalve 128. For example, thevalve 128 can include a valve member 1702 (e.g., a disk, seal, or gasket) and anopening 1704 that connects to the vacuum lumen (not shown). Thevalve member 1702 can be made of rubber or a similar material that forms an airtight seal when placed against theopening 1704. Thevalve member 1702 can be on the skin-piercingassembly 106, such as near the skin-piercingfeature 116. The skin-piercingassembly 106 can be at least partially within theplunger 122, and theopening 1704 can be formed in theplunger 122. Thevalve 128 can be opened when thevalve member 1702 is away from the opening 1704 (e.g., prior to deployment of the skin-piercing feature 116) (FIG. 17A ). Thevalve 128 can be closed when the skin-piercing feature and thevalve member 1702 is against the opening 1704 (e.g., after deployment of the skin-piercing feature 116) (FIG. 17B ). -
FIGS. 18A and 18B are cross-sectional views of a bodilyfluid collection device 100 having a dynamically-generated vacuum mechanism integrated into the skin-piercingassembly 106 configured in accordance with an embodiment the present technology. Thedevice 100 includes thehousing 102, theactuator 104, and the skin-piercingassembly 106. Thehousing 102 includes theupper housing portion 602A and thelower housing portion 602B. Theupper housing portion 602A is shaped to receive theactuator 104. Thelower housing portion 602B includes thebottom surface 110 having theopening 108. - The
actuator 104 is at least partially within theupper housing portion 602A of thedevice 100. Theactuator 104 is mechanically coupled to the skin-piercingassembly 106 via one or more internal device components, such as theplatform 120,plunger 122, and/or sealingmember 124. In some embodiments, theactuator 104 is positioned around at least a portion of theplatform 120, and theplatform 120 is positioned around at least a portion of theplunger 122 and/or sealingmember 124. Theactuator 104,platform 120,plunger 122, and/or sealingmember 124 can be concentrically positioned, such that the longitudinal axes of these components are aligned. - The
actuator 104,platform 120,plunger 122, and sealingmember 124 can be coupled to each other using any suitable combination of complementary interconnecting features (e.g., notches, grooves, projections, tabs, and the like). For example, theplatform 120 can include one or more hook features 1802 that engage one or more complementary notch features 1804 on theplunger 122, such that movement of theplatform 120 along thedeployment direction 112 also moves theplunger 122 along the deployment direction. Theplunger 122 can be a hollow structure with anupper portion 1806A and alower portion 1806B. Theupper portion 1806A can be coupled to theplatform 120, and thelower portion 1806B can be coupled to the sealingmember 124. - The skin-piercing
assembly 106 includes ashaft 1808 at least partially within theplunger 122. Theshaft 1808 has anupper end portion 1810A, alower end portion 1810B, and a flaredportion 1810C. The longitudinal axis of theshaft 1808 can be aligned with thedeployment direction 112 such that theupper end portion 1810A is away from theopening 108 and thelower end portion 1810B is toward theopening 108. The flaredportion 1810C can be between theupper end portion 1810A and thelower end portion 1810B. The flaredportion 1810C can have a larger diameter than theupper end portion 1810A and thelower end portion 1810B. Theshaft 1808 is movable relative to theplunger 122 along thedeployment direction 112 and theretraction direction 114. - The skin-piercing
assembly 106 further includes the skin-piercingfeature 116 and the biasingmember 118. The skin-piercingfeature 116 is coupled to thelower end portion 1810B of theshaft 1808. The biasingmember 118 is positioned within theplunger 122 around at least a portion of theshaft 1808. In some embodiments, the biasingmember 118 is coupled between the flared portion 1806C of theshaft 1808 and theplatform 120, such that the biasingmember 118 drives theshaft 1808 downward relative to theplunger 122 during deployment of the skin-piercingfeature 116. - The sealing
member 124 includes theouter portion 1502A and theinner portion 1502B. Theouter portion 1502A is connected to thehousing 102 and theinner portion 1502B is connected to theplunger 122, thus forming alumen 126 in fluidic connection with theopening 108. In some embodiments, thelower portion 1806B of theplunger 122 includes acollar 1812 that is received within a correspondinggroove 1814 in theinner portion 1502B of the sealingmember 124 to form an airtight seal between theplunger 122 and sealingmember 124. - In some embodiments, the skin-piercing
assembly 106,plunger 122, and sealingmember 124 collectively form avalve 128 fluidically connected to thelumen 126. Thelower portion 1806B of theplunger 122 and theinner portion 1502B of the sealingmember 124 can be open so as to form theopening 1704 of thevalve 128. The flaredportion 1810C of theshaft 1808 of the skin-piercingassembly 106 can serve as thevalve member 1702 of thevalve 128. Thevalve 128 can be opened when thevalve member 1702 is away from the opening 1704 (e.g., when the flaredportion 1810C of theshaft 1808 is toward theupper portion 1806A of the plunger 122) (FIG. 18A ). Thevalve 128 can be closed when thevalve member 1702 is against the opening 1704 (e.g., when the flaredportion 1810C of theshaft 1808 is toward thelower portion 1806B of the plunger 122) (FIG. 18B ). - The device is initially applied to the patient's body with the
opening 108 against the patient's skin, such that thelumen 126 is sealed between the sealingmember 124,plunger 122,housing 102, and the skin. Prior to deployment of the skin-piercing feature 116 (FIG. 18A ), the pressure within thelumen 126 is at or near atmospheric pressure. Thevalve 128 is in the open state, with thevalve member 1702 is away from theopening 1704. During deployment, the biasingmember 118 drives theshaft 1808 along thedeployment direction 112 so that the skin-piercingfeature 116 is moved toward theopening 108. The movement of theshaft 1808 also drives thevalve member 1702 against theopening 1704, thus closing thevalve 128. - During retraction of the skin-piercing
feature 116, thesecond biasing member 634 is between theplatform 120 and thehousing 102, and drives theplatform 120 along theretraction direction 114. The movement of theplatform 120 produces a corresponding movement of theplunger 122 along theretraction direction 114. The movement of theplunger 122 pulls theinner portion 1502B of the sealingmember 124 along theretraction direction 114, resulting in an increase in volume of thelumen 126. Theshaft 1808 maintains its deployed position relative to theplunger 122 such that thevalve 128 remains closed, preventing air from entering the lumen 126 (FIG. 18B ). Accordingly, the pressure within thelumen 126 decreases, producing a vacuum that pulls the patient's skin at least partially through theopening 108 and into thelumen 126. - In some embodiments, the bodily fluid collection devices of the present technology include a skin interface that interacts with the patient's skin and/or bodily fluid to enhance withdrawal of the bodily fluid into the device. For example, the skin interface can control a curvature of the skin pulled into the device (e.g., via the vacuum mechanisms described herein with reference to
FIGS. 13A-18B ) to maintain the incision in an open position that facilitates flow of bodily fluid from the skin. Other purposes of the skin interface is to present a controlled surface on which to collect and direct the flowing bodily fluids to prevent fouling or contamination from the surface of the skin and maintain the skin of the user cleaner. In some embodiments, the skin interface is configured to facilitate rapid removal of bodily fluid from the skin to reduce coagulation of the bodily fluid and/or reduce activation of components within the bodily fluid. For example, in embodiments where the bodily fluid is blood, the skin interface can be configured to quickly remove blood from the skin to reduce blood coagulation and/or platelet activation. -
FIGS. 19A-19E are schematic cross-sectional illustrations of skin interfaces to control skin curvature configured in accordance with an embodiment the present technology.FIG. 19A illustrates askin interface 1900 including thehousing 102 with theopening 108. When a vacuum is applied to theskin 250 from within thehousing 102, a portion of theskin 250 is pulled through theopening 108 and assumes a curved shape. -
FIG. 19B illustrates askin interface 1900 including acurved housing portion 1902. Thecurved housing portion 1902 can be located at least partially around theopening 108 in thehousing 102. When a vacuum is applied to theskin 250 from within thehousing 102, theskin 250 is pulled toward theopening 108 and against the bottom surface of thecurved housing portion 1902, thus assuming a curvature similar to the curvature of thecurved housing portion 1902. -
FIG. 19C illustrates askin interface 1900 including a relatively thinflexible membrane 130. In some embodiments, themembrane 130 has a thickness less than or equal to about 250 μm, or within a range from about 50 μm to about 400 μm. Theflexible membrane 130 is coupled to thehousing 102 in a position at least partially covering theopening 108. Themembrane 130 optionally includes anaperture 1904 to allow the skin-piercing feature (not shown) to pass through. When the bodily fluid collection device is applied to the patient's body, themembrane 130 contacts and couples to theskin 250 to provide an airtight seal against theskin 250. An adhesive may be applied to the bottom surface of themembrane 130 to facilitate sealing against theskin 250. When themembrane 130 is exposed to a vacuum from within thehousing 102, themembrane 130 is pulled at least partially into the interior of thehousing 102 and assumes a curved shape. Due to the seal between theskin 250 and themembrane 130, theskin 250 is also pulled toward theopening 108 and assumes a curvature similar to the curvature of themembrane 130. -
FIG. 19D illustrates askin interface 1900 including a relatively thickflexible membrane 130. Theskin interface 1900 is similar to the interface ofFIG. 19C except that theflexible membrane 130 has an increased thickness. In some embodiments, themembrane 130 has a thickness greater than or equal to about 400 mm, or within a range from about 400 mm to about 800 mm. In some embodiments, a thinner membrane exhibits a higher curvature when exposed to vacuum and produces a higher skin curvature, while a thicker membrane exhibits a lower curvature when exposed to vacuum and produces a lower skin curvature. A higher skin curvature can be advantageous for maintaining the incision in an opened configuration, while a lower skin curvature can be advantageous for reducing bruising or other injuries to the surrounding portions of theskin 250. -
FIG. 19E illustrates askin interface 1900 including aflexible membrane 130 with variable thickness. Theskin interface 1900 is similar to the interfaces ofFIG. 19C-19D , except that theflexible membrane 130 has a variable thickness. In the depicted embodiment, themembrane 130 has acentral portion 1906A and anouter portion 1906B. Thecentral portion 1906A can be thinner and have a higher curvature when exposed to vacuum, while theouter portion 1906B can be thicker and have a lower curvature when exposed to vacuum. For example, thecentral portion 1906A can have a thickness less than or equal to about 300 μm, or within a range from about 50 mm to about 300 μm; and theouter portion 1906B can have a thickness greater than or equal to about 300 μm, or within a range from about 300 μm to about 600 μm. Accordingly, the portion of theskin 250 near thecentral portion 1906A can have a higher curvature than the portion of theskin 250 near theouter portion 1906B. This configuration can be advantageous for maintaining the incision in an open position while reducing injuries to other portions of theskin 250. Alternatively, the thicknesses of thecentral portion 1906A andouter portion 1906B can be reversed, such that thecentral portion 1906A is thicker than theouter portion 1906B. - In some embodiments, the flexible membrane provides more precise control of the curvature of the skin than is achievable using vacuum pressure alone, even over relatively large skin surface areas. Accordingly, a bodily fluid collection device utilizing a flexible membrane as a skin interface can have a larger opening in the housing to allow for bodily fluid to be withdrawn from a greater skin surface area, thus increasing the potential draw volume. For example, the diameter of the opening can be at least about 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm, 16 mm, 17 mm, 18 mm, 19 mm, 20 mm, 21 mm, 22 mm, 23 mm, 24 mm, 25 mm, 26 mm, 27 mm, 28 mm, 29 mm, or 30 mm. In some embodiments, the diameter is within a range from about 9 mm to about 27 mm.
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FIG. 20 is a block diagram of amethod 2000 for withdrawing bodily fluid from a patient's skin using a flexible membrane configured in accordance with an embodiment the present technology. Themethod 2000 can be applied to any embodiment of the bodily fluid collection devices disclosed herein, such as thedevice 100. Additionally, one or more steps of themethod 2000 can be combined with or substituted for any of the steps of the other methods disclosed herein. For example, one or more steps of themethod 2000 can be performed in combination with or as sub-steps ofblock 340 and/or block 350 of themethod 300. - The
method 2000 includes drawing a vacuum within the device (block 2010). The vacuum can be generating using any of the vacuum mechanisms disclosed herein, such as the vacuum mechanisms described with reference toFIGS. 13A-18B . Themethod 2000 further includes pulling a flexible membrane at least partially within the device (block 2020). For example, the flexible membrane can be coupled to the bottom surface of the housing in a position covering at least a portion of the opening, and the flexible membrane can be pulled at least partially through the opening when exposed to the vacuum. - The method further includes contacting a patient's skin with the flexible membrane to control a curvature of the skin (block 2030). In some embodiments, the patient's skin is also pulled at least partially through the opening and into the device. The flexible membrane can assume a curved shape when exposed to the vacuum, and the patient's skin can be sealed against the flexible membrane so as to assume a similar curved shape.
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FIGS. 21A-21C are cross-sectional and perspective views of theflexible membrane 130 of a bodily fluid collection device configured in accordance with an embodiment the present technology. The device includes theopening 108 formed in thehousing 102, and themembrane 130 is coupled to thehousing 102 and covers at least a portion of theopening 108. Optionally, themembrane 130 can include anaperture 1904 to allow the skin-piercing feature of the device to pass through themembrane 130 during deployment. Alternatively, themembrane 130 may be provided without any aperture, and the skin-piercing feature can puncture themembrane 130 during deployment to form theaperture 1904. Prior to being exposed to a vacuum (FIG. 21A ), themembrane 130 is in a generally planar configuration, with little or no curvature. When a vacuum is drawn within thehousing 102 of the device (FIG. 21B ), themembrane 130 is pulled at least partially within thehousing 102 and into a curved shape. Bodily fluid is withdrawn into thehousing 102 via theaperture 1904, and can be directed into a collection reservoir (not shown) via achannel 2100. -
FIG. 22 is an exploded view of theflexible membrane 130 configured in accordance with an embodiment the present technology. Themembrane 130 includes afilm 2200, afirst adhesive layer 2202, and asecond adhesive layer 2204. Thefilm 2200 can be a thin film of a flexible material, such as polyurethane or silicone. Thefirst adhesive layer 2202 can be a double-sided adhesive that adheres to both thefilm 2200 and the housing of the bodily fluid collection device. Thesecond adhesive layer 2204 can be a double-sided adhesive that adheres to both thefilm 2200 and a portion of the patient's skin. The adhesive material of the first and secondadhesive layers flexible membrane 130 forms an airtight seal between the housing and the patient's skin. In alternative embodiments, thefirst adhesive layer 2202,second adhesive layer 2204, or both may be omitted from themembrane 130. - The
film 2200 can include anaperture 1904 for the skin-piercing feature to pass through during deployment. Thefirst adhesive layer 2202 can include anaperture 2206 formed within a central portion of thefirst adhesive layer 2202. Thesecond adhesive layer 2204 can include anaperture 2208 formed within a central portion of thesecond adhesive layer 2204. Theapertures - The
membrane 130 can be provided with aliner 2210 that protects themembrane 130 prior to use, e.g., during storage and/or transportation. The liner 2406 can be removed to expose thesecond adhesive layer 2204 so that theflexible membrane 130 can be applied to and sealed against the patient's skin. Optionally, theliner 2210 can include atab portion 2212 that extends beyond the housing of the device (e.g., as shown inFIG. 6A ) to facilitate removal of theliner 2210. - In some embodiments, the membrane can be directly cast into the base of the bodily fluid collection device itself using thermoplastic elastomeric materials or silicone materials. This manufacturing method would remove the need for the
first adhesive layer 2202 and as these manufacturing methods do not require the membrane to be planar, they would enable the creation of structural or functional features on the membrane itself. - In some embodiments, the flexible membranes of the present technology include one or more surface features and/or treatments to enhance flow of the bodily fluid from the patient's skin and into the device. For the example, the surface features and/or treatments can be configured to reduce coagulation of the bodily fluid (e.g., blood coagulation), reduce adhesion of the bodily fluid to the patient's skin, reduce adhesion of the bodily fluid to the membrane, direct flow of the bodily fluid toward a desired location (e.g., toward the collection reservoir), and/or direct flow of the bodily fluid away from an undesired location. The surface features and/or treatments can be on a lower surface of the membrane (e.g., the surface toward the patient's skin), the upper surface of the membrane (e.g., the surface away from the patient's skin), or both. The upper and lower surfaces of the membrane can have the same features and/or treatments, or can have different features and/or treatments.
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FIGS. 23A-23E are various views of portions of flexible membranes with different surface features and/or treatments configured in accordance with an embodiment the present technology. For example,FIG. 23A is a schematic illustration of a top view of theflexible membrane 130 without surface features and/or treatments. Themembrane 130 includes an aperture 1904 (e.g., pre-formed in themembrane 130 or formed by the skin-piercing feature) through whichbodily fluid 2300 is withdrawn from the patient'sskin 250. The fluid 2300 may spread and smear across theskin 250 and/ormembrane 130, thus making it more difficult to collect thefluid 2300. -
FIG. 23B is a schematic illustration of a top view of theflexible membrane 130 with micropatterned features 2302. The micropatterned features 2302 can include various combinations of channels, ridges, grooves, surface modifications, or patterned surface treatments or coatings, and the like. The micropatterned features 2302 can be shaped and positioned to direct flow of the bodily fluid toward a desired location, such as toward the collection reservoir. For example, in the embodiment ofFIG. 23B , the micropatterned features 2302 include alinear channel 2304 extending from theaperture 1904 toward the reservoir. Bodily fluid 2300 withdrawn from theskin 250 can flow into thechannel 2304 and toward the reservoir. In some embodiments where multiple incisions are made on the same membrane these features can be used to combine the bodily fluids from multiple incisions or alternatively to keep them separate and allow different treatments to be made to the flowing fluids. Furthermore, this approach can allow the direction of the multiple flows of bodily fluids toward different or separate reservoirs or containers. -
FIG. 23C is a perspective top view of a portion of theflexible membrane 130 with micropatterned features 2302. Thefeatures 2302 include acircular ridge 2306 defining achamber 2308 that contains the bodily fluid. Theridge 2306 can define anopening 2310 in thechamber 2308 that is oriented toward the collection reservoir to direct the bodily fluid into the reservoir. Thefeatures 2302 can also include ridges,parallel ridges 2312, or multiple ridges within thechamber 2308. Theridges 2312 can be on either side of the location where the skin-piercing feature punctures themembrane 130 to direct bodily fluid toward theopening 2310, or along the path of the flow to act as a capillary guidance to the flow of fluids. Thefeatures 2302 can also include a pair ofangled ridges 2314 within thechamber 2308 near theopening 2310. Theangled ridges 2314 can serve to funnel bodily fluid from within thechamber 2308 toward theopening 2310. -
FIG. 23D is a schematic illustration of a top view of a portion of theflexible membrane 130 with a hydrophobic coating 2316 (e.g., a silicone coating). Thehydrophobic coating 2316 can be applied to the membrane 130 (e.g., by spray-coating). Alternatively, themembrane 130 itself can be made of a hydrophobic material. When the bodily fluid 2300 contacts thecoating 2316, it forms into droplets that move easily across the surface of themembrane 130 with little or no sticking. -
FIG. 23E is a schematic illustration of a top view of a portion of theflexible membrane 130 with ananticoagulant coating 2318. In some embodiments, theanticoagulant coating 2318 includes spray-coated EDTA. Theanticoagulant coating 2318 can reduce the coagulation of the bodily fluid, thus improving flow into the reservoir. -
FIGS. 24A-24F are cross-sectional views of housing features to control flow of bodily fluid along aflexible membrane 130 configured in accordance with an embodiment the present technology. In some embodiments, accumulation of bodily fluid 2300 at theouter portion 1906B of theflexible membrane 130 is undesirable. Such accumulation may occur if the angle between theouter portion 1906B and the portion of thehousing 102 adjacent to theouter portion 1906B (“base portion 2400”) is sufficiently small, e.g., less than about 90 degrees. For example, although the angle between theouter portion 1906B and thebase portion 2400 may initially be greater than or equal to about 90 degrees (FIG. 24A ), the angle may decrease to less than 90 degrees when themembrane 130 is curved (FIG. 24B ). The decreased angle may pull bodily fluid between theouter portion 1906B and thebase portion 2400, e.g., via capillary action. -
FIGS. 24C and 24D illustrate ashelf 2402 to reduce flow of bodily fluid between theouter portion 1906B and thebase portion 2400. Theshelf 2402 can be formed in thebase portion 2400 and can extend radially inward to partially cover theopening 108. When themembrane 130 is curved (FIG. 24D ),bodily fluid 2300 can flow onto theshelf 2402, rather than becoming trapped between thebase portion 2400 and themembrane 130. -
FIGS. 24E and 24F illustrate anangled base portion 2400 to reduce flow of bodily fluid between theouter portion 1906B and thebase portion 2400. The geometry of the angled basedportion 2400 can be configured such that when themembrane 130 is curved (FIG. 24F ), the angle between thebase portion 2400 and theouter portion 1906B of themembrane 130 is sufficiently large to avoid drawing bodily fluid 2300 between theouter portion 1906B and thebase portion 2400. -
FIGS. 25A-25F are cross-sectional and top views of awicking element 2500 for directing flow of abodily fluid 2300 configured in accordance with an embodiment the present technology. Thewicking element 2500 can be used in combination with or as an alternative to the flexible membranes disclosed herein. Thewicking element 2500 can be made of an absorbent material, and can optionally include an anticoagulant. Thewicking element 2500 can include afirst wicking portion 2502A and asecond wicking portion 2502B. Thefirst wicking portion 2502A can be shaped to at least partially cover theopening 108 of thehousing 102, and can optionally include an aperture for the skin-piercingfeature 116 to pass through. Thesecond wicking portion 2502B can have an elongated shape configured to direct bodily fluid 2300 into thehousing 102 toward the collection reservoir. - In some embodiments, the
wicking element 2500 is positioned over theflexible membrane 130, with thefirst wicking portion 2502A over theaperture 1904 in themembrane 130, and thesecond wicking portion 2502B extending along themembrane 130 toward the interior of the housing (FIG. 25A (cross-sectional view) and 25B (top view)). The skin-piercingfeature 116 can be deployed through thefirst wicking portion 2502A to pierce the patient's skin (FIG. 25C (cross-sectional view) and 25D (top view)). The skin-piercingfeature 116 can subsequently be retracted through thefirst wicking portion 2502A to permit withdrawal of bodily fluid 2300 (FIG. 25E (cross-sectional view) and 25F (top view)). A first portion of thebodily fluid 2300 can be absorbed into thewicking element 2500. Once thewicking element 2500 is saturated, a remaining portion of thebodily fluid 2300 can flow between thesecond wicking portion 2502B and theflexible membrane 130 toward the collection reservoir. In some embodiments, the first portion of thebodily fluid 2300 includes contaminants or is otherwise undesirable for testing and analysis of thebodily fluid 2300. Accordingly, thewicking element 2500 can be used to absorb and discard the first portion of thebodily fluid 2300, while directing the remaining portion of thebodily fluid 2300 into the housing and reservoir for collection. Furthermore, the wicking element can be utilized to guide the flow of fluids over the membrane or plastic and deliver chemical treatments to the fluid rapidly after it is extracted from the skin. - This disclosure is not intended to be exhaustive or to limit the present technology to the precise forms disclosed herein. Although specific embodiments are disclosed herein for illustrative purposes, various equivalent modifications are possible without deviating from the present technology, as those of ordinary skill in the relevant art will recognize. In some cases, well-known structures and functions have not been shown and/or described in detail to avoid unnecessarily obscuring the description of the embodiments of the present technology. Although steps of methods may be presented herein in a particular order, in alternative embodiments the steps may have another suitable order. Similarly, certain aspects of the present technology disclosed in the context of particular embodiments can be combined or eliminated in other embodiments. Furthermore, while advantages associated with certain embodiments may have been disclosed in the context of those embodiments, other embodiments can also exhibit such advantages, and not all embodiments need necessarily exhibit such advantages or other advantages disclosed herein to fall within the scope of the present technology. Accordingly, this disclosure and associated technology can encompass other embodiments not expressly shown and/or described herein.
- Throughout this disclosure, the singular terms “a,” “an,” and “the” include plural referents unless the context clearly indicates otherwise. Similarly, unless the word “or” is expressly limited to mean only a single item exclusive from the other items in reference to a list of two or more items, then the use of “or” in such a list is to be interpreted as including (a) any single item in the list, (b) all of the items in the list, or (c) any combination of the items in the list. Additionally, the terms “comprising” and the like are used throughout this disclosure to mean including at least the recited feature(s) such that any greater number of the same feature(s) and/or one or more additional types of features are not precluded. Directional terms, such as “upper,” “lower,” “front,” “back,” “vertical,” and “horizontal,” may be used herein to express and clarify the relationship between various elements. It should be understood that such terms do not denote absolute orientation. Reference herein to “one embodiment,” “an embodiment,” or similar formulations means that a particular feature, structure, operation, or characteristic described in connection with the embodiment can be included in at least one embodiment of the present technology. Thus, the appearances of such phrases or formulations herein are not necessarily all referring to the same embodiment. Furthermore, various particular features, structures, operations, or characteristics may be combined in any suitable manner in one or more embodiments.
- From the foregoing, it will be appreciated that specific embodiments of the present technology have been described herein for purposes of illustration, but that various modifications may be made without deviating from the scope of the present technology. Accordingly, the present technology is not limited except as by the appended claims.
Claims (20)
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EP3820368A4 (en) | 2022-05-11 |
EP3820368B1 (en) | 2023-08-09 |
JP2022500125A (en) | 2022-01-04 |
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CN111657965B (en) | 2024-03-22 |
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JP7460607B2 (en) | 2024-04-02 |
CN111295138A (en) | 2020-06-16 |
US11510659B2 (en) | 2022-11-29 |
EP4278983A2 (en) | 2023-11-22 |
EP3820368A1 (en) | 2021-05-19 |
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